US20090286008A1 - Laser-produced porous surface - Google Patents
Laser-produced porous surface Download PDFInfo
- Publication number
- US20090286008A1 US20090286008A1 US12/386,679 US38667909A US2009286008A1 US 20090286008 A1 US20090286008 A1 US 20090286008A1 US 38667909 A US38667909 A US 38667909A US 2009286008 A1 US2009286008 A1 US 2009286008A1
- Authority
- US
- United States
- Prior art keywords
- layer
- laser
- powder
- metal powder
- titanium
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
Images
Classifications
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B33—ADDITIVE MANUFACTURING TECHNOLOGY
- B33Y—ADDITIVE MANUFACTURING, i.e. MANUFACTURING OF THREE-DIMENSIONAL [3-D] OBJECTS BY ADDITIVE DEPOSITION, ADDITIVE AGGLOMERATION OR ADDITIVE LAYERING, e.g. BY 3-D PRINTING, STEREOLITHOGRAPHY OR SELECTIVE LASER SINTERING
- B33Y10/00—Processes of additive manufacturing
-
- C—CHEMISTRY; METALLURGY
- C23—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; CHEMICAL SURFACE TREATMENT; DIFFUSION TREATMENT OF METALLIC MATERIAL; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL; INHIBITING CORROSION OF METALLIC MATERIAL OR INCRUSTATION IN GENERAL
- C23C—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; SURFACE TREATMENT OF METALLIC MATERIAL BY DIFFUSION INTO THE SURFACE, BY CHEMICAL CONVERSION OR SUBSTITUTION; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL
- C23C26/00—Coating not provided for in groups C23C2/00 - C23C24/00
- C23C26/02—Coating not provided for in groups C23C2/00 - C23C24/00 applying molten material to the substrate
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
- A61F2/30771—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth applied in original prostheses, e.g. holes or grooves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
- A61F2/30907—Nets or sleeves applied to surface of prostheses or in cement
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/3094—Designing or manufacturing processes
- A61F2/30965—Reinforcing the prosthesis by embedding particles or fibres during moulding or dipping
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F10/00—Additive manufacturing of workpieces or articles from metallic powder
- B22F10/20—Direct sintering or melting
- B22F10/28—Powder bed fusion, e.g. selective laser melting [SLM] or electron beam melting [EBM]
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F10/00—Additive manufacturing of workpieces or articles from metallic powder
- B22F10/30—Process control
- B22F10/38—Process control to achieve specific product aspects, e.g. surface smoothness, density, porosity or hollow structures
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F10/00—Additive manufacturing of workpieces or articles from metallic powder
- B22F10/80—Data acquisition or data processing
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F3/00—Manufacture of workpieces or articles from metallic powder characterised by the manner of compacting or sintering; Apparatus specially adapted therefor ; Presses and furnaces
- B22F3/10—Sintering only
- B22F3/11—Making porous workpieces or articles
- B22F3/1103—Making porous workpieces or articles with particular physical characteristics
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F3/00—Manufacture of workpieces or articles from metallic powder characterised by the manner of compacting or sintering; Apparatus specially adapted therefor ; Presses and furnaces
- B22F3/10—Sintering only
- B22F3/11—Making porous workpieces or articles
- B22F3/1103—Making porous workpieces or articles with particular physical characteristics
- B22F3/1115—Making porous workpieces or articles with particular physical characteristics comprising complex forms, e.g. honeycombs
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F7/00—Manufacture of composite layers, workpieces, or articles, comprising metallic powder, by sintering the powder, with or without compacting wherein at least one part is obtained by sintering or compression
- B22F7/002—Manufacture of composite layers, workpieces, or articles, comprising metallic powder, by sintering the powder, with or without compacting wherein at least one part is obtained by sintering or compression of porous nature
- B22F7/004—Manufacture of composite layers, workpieces, or articles, comprising metallic powder, by sintering the powder, with or without compacting wherein at least one part is obtained by sintering or compression of porous nature comprising at least one non-porous part
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K26/00—Working by laser beam, e.g. welding, cutting or boring
- B23K26/36—Removing material
- B23K26/38—Removing material by boring or cutting
- B23K26/382—Removing material by boring or cutting by boring
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K26/00—Working by laser beam, e.g. welding, cutting or boring
- B23K26/36—Removing material
- B23K26/40—Removing material taking account of the properties of the material involved
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
- B29C—SHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
- B29C64/00—Additive manufacturing, i.e. manufacturing of three-dimensional [3D] objects by additive deposition, additive agglomeration or additive layering, e.g. by 3D printing, stereolithography or selective laser sintering
- B29C64/10—Processes of additive manufacturing
- B29C64/141—Processes of additive manufacturing using only solid materials
- B29C64/153—Processes of additive manufacturing using only solid materials using layers of powder being selectively joined, e.g. by selective laser sintering or melting
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B33—ADDITIVE MANUFACTURING TECHNOLOGY
- B33Y—ADDITIVE MANUFACTURING, i.e. MANUFACTURING OF THREE-DIMENSIONAL [3-D] OBJECTS BY ADDITIVE DEPOSITION, ADDITIVE AGGLOMERATION OR ADDITIVE LAYERING, e.g. BY 3-D PRINTING, STEREOLITHOGRAPHY OR SELECTIVE LASER SINTERING
- B33Y70/00—Materials specially adapted for additive manufacturing
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B33—ADDITIVE MANUFACTURING TECHNOLOGY
- B33Y—ADDITIVE MANUFACTURING, i.e. MANUFACTURING OF THREE-DIMENSIONAL [3-D] OBJECTS BY ADDITIVE DEPOSITION, ADDITIVE AGGLOMERATION OR ADDITIVE LAYERING, e.g. BY 3-D PRINTING, STEREOLITHOGRAPHY OR SELECTIVE LASER SINTERING
- B33Y80/00—Products made by additive manufacturing
-
- C—CHEMISTRY; METALLURGY
- C23—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; CHEMICAL SURFACE TREATMENT; DIFFUSION TREATMENT OF METALLIC MATERIAL; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL; INHIBITING CORROSION OF METALLIC MATERIAL OR INCRUSTATION IN GENERAL
- C23C—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; SURFACE TREATMENT OF METALLIC MATERIAL BY DIFFUSION INTO THE SURFACE, BY CHEMICAL CONVERSION OR SUBSTITUTION; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL
- C23C24/00—Coating starting from inorganic powder
- C23C24/02—Coating starting from inorganic powder by application of pressure only
- C23C24/04—Impact or kinetic deposition of particles
-
- C—CHEMISTRY; METALLURGY
- C23—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; CHEMICAL SURFACE TREATMENT; DIFFUSION TREATMENT OF METALLIC MATERIAL; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL; INHIBITING CORROSION OF METALLIC MATERIAL OR INCRUSTATION IN GENERAL
- C23C—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; SURFACE TREATMENT OF METALLIC MATERIAL BY DIFFUSION INTO THE SURFACE, BY CHEMICAL CONVERSION OR SUBSTITUTION; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL
- C23C24/00—Coating starting from inorganic powder
- C23C24/08—Coating starting from inorganic powder by application of heat or pressure and heat
- C23C24/10—Coating starting from inorganic powder by application of heat or pressure and heat with intermediate formation of a liquid phase in the layer
-
- C—CHEMISTRY; METALLURGY
- C23—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; CHEMICAL SURFACE TREATMENT; DIFFUSION TREATMENT OF METALLIC MATERIAL; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL; INHIBITING CORROSION OF METALLIC MATERIAL OR INCRUSTATION IN GENERAL
- C23C—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; SURFACE TREATMENT OF METALLIC MATERIAL BY DIFFUSION INTO THE SURFACE, BY CHEMICAL CONVERSION OR SUBSTITUTION; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL
- C23C4/00—Coating by spraying the coating material in the molten state, e.g. by flame, plasma or electric discharge
- C23C4/02—Pretreatment of the material to be coated, e.g. for coating on selected surface areas
-
- C—CHEMISTRY; METALLURGY
- C23—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; CHEMICAL SURFACE TREATMENT; DIFFUSION TREATMENT OF METALLIC MATERIAL; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL; INHIBITING CORROSION OF METALLIC MATERIAL OR INCRUSTATION IN GENERAL
- C23C—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; SURFACE TREATMENT OF METALLIC MATERIAL BY DIFFUSION INTO THE SURFACE, BY CHEMICAL CONVERSION OR SUBSTITUTION; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL
- C23C4/00—Coating by spraying the coating material in the molten state, e.g. by flame, plasma or electric discharge
- C23C4/12—Coating by spraying the coating material in the molten state, e.g. by flame, plasma or electric discharge characterised by the method of spraying
-
- C—CHEMISTRY; METALLURGY
- C23—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; CHEMICAL SURFACE TREATMENT; DIFFUSION TREATMENT OF METALLIC MATERIAL; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL; INHIBITING CORROSION OF METALLIC MATERIAL OR INCRUSTATION IN GENERAL
- C23C—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; SURFACE TREATMENT OF METALLIC MATERIAL BY DIFFUSION INTO THE SURFACE, BY CHEMICAL CONVERSION OR SUBSTITUTION; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL
- C23C4/00—Coating by spraying the coating material in the molten state, e.g. by flame, plasma or electric discharge
- C23C4/18—After-treatment
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/3094—Designing or manufacturing processes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/32—Joints for the hip
- A61F2/34—Acetabular cups
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/32—Joints for the hip
- A61F2/36—Femoral heads ; Femoral endoprostheses
- A61F2/3662—Femoral shafts
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/38—Joints for elbows or knees
- A61F2/3859—Femoral components
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/38—Joints for elbows or knees
- A61F2/389—Tibial components
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
- A61F2002/30003—Material related properties of the prosthesis or of a coating on the prosthesis
- A61F2002/30004—Material related properties of the prosthesis or of a coating on the prosthesis the prosthesis being made from materials having different values of a given property at different locations within the same prosthesis
- A61F2002/30006—Material related properties of the prosthesis or of a coating on the prosthesis the prosthesis being made from materials having different values of a given property at different locations within the same prosthesis differing in density or specific weight
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
- A61F2002/30003—Material related properties of the prosthesis or of a coating on the prosthesis
- A61F2002/30004—Material related properties of the prosthesis or of a coating on the prosthesis the prosthesis being made from materials having different values of a given property at different locations within the same prosthesis
- A61F2002/30011—Material related properties of the prosthesis or of a coating on the prosthesis the prosthesis being made from materials having different values of a given property at different locations within the same prosthesis differing in porosity
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
- A61F2002/30108—Shapes
- A61F2002/3011—Cross-sections or two-dimensional shapes
- A61F2002/30138—Convex polygonal shapes
- A61F2002/30153—Convex polygonal shapes rectangular
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
- A61F2002/30108—Shapes
- A61F2002/30199—Three-dimensional shapes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
- A61F2002/30108—Shapes
- A61F2002/30199—Three-dimensional shapes
- A61F2002/30261—Three-dimensional shapes parallelepipedal
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
- A61F2/30907—Nets or sleeves applied to surface of prostheses or in cement
- A61F2002/30909—Nets
- A61F2002/30915—Nets made of a stack of bonded perforated sheets, grids or wire meshes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
- A61F2002/3092—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth having an open-celled or open-pored structure
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
- A61F2002/30929—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth having at least two superposed coatings
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
- A61F2002/3093—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth for promoting ingrowth of bone tissue
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/3094—Designing or manufacturing processes
- A61F2002/30968—Sintering
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/3094—Designing or manufacturing processes
- A61F2002/3097—Designing or manufacturing processes using laser
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/3094—Designing or manufacturing processes
- A61F2002/30971—Laminates, i.e. layered products
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0002—Two-dimensional shapes, e.g. cross-sections
- A61F2230/0017—Angular shapes
- A61F2230/0019—Angular shapes rectangular
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0063—Three-dimensional shapes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0063—Three-dimensional shapes
- A61F2230/0082—Three-dimensional shapes parallelepipedal
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0014—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
- A61F2250/0015—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in density or specific weight
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0014—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
- A61F2250/0023—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in porosity
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00017—Iron- or Fe-based alloys, e.g. stainless steel
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00023—Titanium or titanium-based alloys, e.g. Ti-Ni alloys
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00029—Cobalt-based alloys, e.g. Co-Cr alloys or Vitallium
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00035—Other metals or alloys
- A61F2310/00095—Niobium or Nb-based alloys
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00035—Other metals or alloys
- A61F2310/00131—Tantalum or Ta-based alloys
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00389—The prosthesis being coated or covered with a particular material
- A61F2310/00395—Coating or prosthesis-covering structure made of metals or of alloys
- A61F2310/00401—Coating made of iron, of stainless steel or of other Fe-based alloys
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00389—The prosthesis being coated or covered with a particular material
- A61F2310/00395—Coating or prosthesis-covering structure made of metals or of alloys
- A61F2310/00407—Coating made of titanium or of Ti-based alloys
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00389—The prosthesis being coated or covered with a particular material
- A61F2310/00395—Coating or prosthesis-covering structure made of metals or of alloys
- A61F2310/00413—Coating made of cobalt or of Co-based alloys
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00389—The prosthesis being coated or covered with a particular material
- A61F2310/00395—Coating or prosthesis-covering structure made of metals or of alloys
- A61F2310/00419—Other metals
- A61F2310/00491—Coating made of niobium or Nb-based alloys
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00389—The prosthesis being coated or covered with a particular material
- A61F2310/00395—Coating or prosthesis-covering structure made of metals or of alloys
- A61F2310/00419—Other metals
- A61F2310/00544—Coating made of tantalum or Ta-based alloys
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F10/00—Additive manufacturing of workpieces or articles from metallic powder
- B22F10/30—Process control
- B22F10/36—Process control of energy beam parameters
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F10/00—Additive manufacturing of workpieces or articles from metallic powder
- B22F10/30—Process control
- B22F10/36—Process control of energy beam parameters
- B22F10/366—Scanning parameters, e.g. hatch distance or scanning strategy
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F10/00—Additive manufacturing of workpieces or articles from metallic powder
- B22F10/30—Process control
- B22F10/37—Process control of powder bed aspects, e.g. density
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F2301/00—Metallic composition of the powder or its coating
- B22F2301/15—Nickel or cobalt
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F2301/00—Metallic composition of the powder or its coating
- B22F2301/20—Refractory metals
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F2301/00—Metallic composition of the powder or its coating
- B22F2301/20—Refractory metals
- B22F2301/205—Titanium, zirconium or hafnium
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F2301/00—Metallic composition of the powder or its coating
- B22F2301/35—Iron
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F2999/00—Aspects linked to processes or compositions used in powder metallurgy
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K2101/00—Articles made by soldering, welding or cutting
- B23K2101/34—Coated articles, e.g. plated or painted; Surface treated articles
- B23K2101/35—Surface treated articles
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K2103/00—Materials to be soldered, welded or cut
- B23K2103/02—Iron or ferrous alloys
- B23K2103/04—Steel or steel alloys
- B23K2103/05—Stainless steel
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K2103/00—Materials to be soldered, welded or cut
- B23K2103/08—Non-ferrous metals or alloys
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K2103/00—Materials to be soldered, welded or cut
- B23K2103/08—Non-ferrous metals or alloys
- B23K2103/14—Titanium or alloys thereof
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K2103/00—Materials to be soldered, welded or cut
- B23K2103/18—Dissimilar materials
- B23K2103/26—Alloys of Nickel and Cobalt and Chromium
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K2103/00—Materials to be soldered, welded or cut
- B23K2103/50—Inorganic material, e.g. metals, not provided for in B23K2103/02 – B23K2103/26
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
- Y02P—CLIMATE CHANGE MITIGATION TECHNOLOGIES IN THE PRODUCTION OR PROCESSING OF GOODS
- Y02P10/00—Technologies related to metal processing
- Y02P10/25—Process efficiency
Definitions
- the present invention relates to a porous surface and a method for forming the same, which uses a directed energy beam to selectively remelt a powder to produce a part.
- this invention relates to a computer-aided laser apparatus, which sequentially remelts a plurality of powder layers to build the designed part in a layer-by-layer fashion.
- the present application is particularly directed toward a method of forming a porous and partially porous metallic structure.
- the selective laser remelting and sintering technologies have enabled the direct manufacture of solid or dense three-dimensional articles of high resolution and dimensional accuracy from a variety of materials including wax, metal powders with binders, polycarbonate, nylon, other plastics and composite materials, such as polymer-coated metals and ceramics.
- the metal articles formed in these ways have been quite dense, for example, having densities of up to 70% to 80% of fully dense (prior to any infiltration).
- Prior applications of this technology have strived to increase the density of the metal structures formed by the remelting or sintering processes.
- the field of rapid prototyping of parts has focused on providing high strength, high density, parts for use and design in production of many useful articles, including metal parts.
- the present invention relates to a method for producing a three-dimensional porous structure particularly for use with tissue ingrowth.
- a layer of metallic powder is deposited onto a substrate or a build platform.
- Preferred metals for the powder include titanium, titanium alloys, stainless steel, cobalt chrome alloys, tantalum or niobium.
- a laser beam with predetermined settings scans the powder layer causing the powder to preferentially remelt and consequently solidify with a decreased density, resulting from an increase in porosity as compared to a solid metal.
- the range of the laser's power may be between 5 W and 1000 W.
- successive offset layering and remelting are continued until the porous part has been successfully completed.
- the benefit of the part formed is that that decreased density increases porosity thus enabling the part to be used for, among other things, tissue ingrowth.
- the first layer of metallic powder is deposited onto a solid base or core and fused thereto.
- Preferred metals used for the core include titanium, titanium alloys, stainless steel, cobalt chrome alloys, tantalum and niobium.
- Successive powder layers of the same or different materials are once again added in a layer-by-layer fashion until the part is completed.
- This embodiment has the desired effect of providing a structure in which the porosity may be increased as the structure is built, resulting in a graded profile in which the mechanical properties will also be reduced outwards from the core. This will allow the formed part to be used for, among other things, medical implants and prosthesis, but yet still include a surface for tissue ingrowth.
- the method of producing a three-dimensional porous tissue ingrowth structure may include depositing a first layer of a powder made from a metal selected from the group consisting of titanium, titanium alloys, stainless steel, cobalt chrome alloys, tantalum and niobium, onto a substrate. Followinged by scanning a laser beam at least once over the first layer of powder.
- the laser beam having a power (P) in Joule per seconds with a scanning speed (v) in millimeters per second with a range between 80 and 400 mms. and a beam overlap (b) in millimeters of between 50% and ⁇ 1200%.
- P power
- v scanning speed
- b beam overlap
- At least one additional layer of powder is deposited and then the laser scanning steps for each successive layer are repeated until a desired web height is reached.
- at least one laser scan is carried out angled relative to another laser scan in order to develop an interconnecting or non-interconnecting porosity.
- the thickness of the first layer and said successive layers of powder is between 5 ⁇ m-2000 ⁇ m.
- the laser can be applied either continuously or in a pulse manner, with the frequency of the pulse being in the range of approximately 1 KHz to 50 KHz.
- the method is carried out under an inert atmosphere, more preferably specifically an Argon inert atmosphere.
- a third metal may be used to act as an intermediate.
- the third metal would act as a bond coat between the core and first layer of powder.
- the core may be integral with the resultant porous ingrowth structure and impart additional physical properties to the overall construct.
- the core may also be detachable from the resultant porous surface buildup.
- FIG. 1 is a diagrammatic illustration of the apparatus used to make test samples according to the processes of the present invention
- FIG. 2 is a photographic image showing an array of samples produced by the processes as performed by the apparatus of FIG. 1 ;
- FIG. 3 is a table showing a series of parameters used for the samples of FIG. 2 ;
- FIGS. 4 to 10 are scanning electron microscope images of the surface structure of various samples made by the method according to the invention.
- FIG. 11 is a scanning electron microscope micrograph taken from a porous Ti sintered structure
- FIG. 12 is an optical image of a section through a sample showing the microstructure
- FIG. 13 is an image detailing surface structures
- FIGS. 14 and 15 are non-contact surface profilimetry images detailing plan views of the samples.
- FIGS. 16 to 25 are scanning electron microscope micrographs produced prior to multi-layer builds shown in FIGS. 7 and 8 .
- FIG. 26 indicates the metallography and spectra of a typical bond coat structure.
- FIG. 27 shows the effect of line spacing on pore size.
- FIG. 28 a - f are examples of typical waffle structures.
- FIG. 29 is a trabecular bone-type structure constructed from a micro CT scan.
- FIG. 30 shows typical freestanding structures.
- FIG. 31 shows a freestanding structure built using the preferred scanning strategy.
- the present invention relates to a method of forming porous and partially porous metallic structures which are particularly but not exclusively applicable for use in hard or soft tissue interlock structures for medical implants and prosthesis.
- the method makes use of laser technology by employing a variety of scanning strategies.
- Typical metal and metal alloys employed include stainless steel, cobalt chromium alloys, titanium and its alloys, tantalum and niobium, all of which have been used in medical device applications.
- the present invention can be used for such medical device applications where bone and soft tissue interlock with a component is required, or where a controlled structure is required to more closely match the mechanical properties of the device with surrounding tissue. Additionally, the present invention may be employed to enhance the biocompatibility of a porous structure with animal tissue. With these advantages in mind, a structure may be created using specific dimensions required to accommodate a particular patient.
- One particular intention of the present invention is to produce a three-dimensional structure using a direct laser remelt process, for example, for building structures with or without a solid base or core.
- the three-dimensional structure could be used to provide a porous outer layer to form a bone in-growth structure.
- the porous structure when applied to a core, could be used to form a prosthesis with a defined stiffness to both fulfill the requirement of a modulus match with surrounding tissue and provide interconnected porosity for tissue interlock.
- a further use could be to form an all-porous structure with grade pore size to interact with more than one type of tissue.
- the process can be used to build on a solid base or core with an outer porous surface, the porosity of which is constant or which varies.
- the base or core materials to which the process is applied is either titanium and its alloys, stainless steel, cobalt chrome alloys, tantalum or niobium.
- the preferred surface coatings are titanium, cobalt chrome and tantalum but both stainless steel and niobium can also be used.
- Fully porous structures may be built from any of the materials tested, with the preferred material being titanium.
- One intention of the present invention is to produce a method which can be exploited on a commercial basis for the production of, for example, bone interlock surfaces on a device although it has many other uses.
- a method of forming a three-dimensional structure includes building the shape by laser melting powdered titanium and titanium alloys, stainless steel, cobalt chrome alloys, tantalum or niobium.
- the laser may be a continuous wave or pulsed laser beam.
- the method can be performed so that the structure is porous and if desired, the pores can be interconnecting to provide an interconnected porosity.
- the method can include using a base or core of cobalt chrome alloy, titanium or alloy, stainless steel, niobium and tantalum, on which to build a porous layer of any one of the aforementioned metals and alloys by laser melting using a continuous or pulsed laser beam.
- a base or core of cobalt chrome alloy, titanium or alloy, stainless steel, niobium and tantalum on which to build a porous layer of any one of the aforementioned metals and alloys by laser melting using a continuous or pulsed laser beam.
- a mixture of desired mixed materials may be employed.
- the method can be applied to an existing article made from cobalt chrome, titanium or titanium alloys, stainless steel, tantalum or niobium, such as an orthopedic implant, to produce a porous outer layer from any of the aforementioned metals or alloys to provide a bone in-growth structure.
- a cleaning operation to ensure a contaminant-free surface may be employed prior to the deposition of any powder onto a substrate.
- this process may include a solvent wash followed by a cleaning scan of the laser beam without the presence of particles.
- a coating process may be employed.
- the coating process includes applying a third metal directly to the substrate, which has a higher bond strength to the substrate then does the first layer of powder. This process is particularly useful when the substrate and first powder layer are of different materials.
- the process of coating the substrate may be accomplished using known processes including laser deposition, plasma coating, cold gas dynamic spraying or similar techniques.
- One example of the coating process includes using either niobium or tantalum as an interface between a cobalt chrome alloy substrate and a first layer of titanium powder.
- the present invention can also include a laser melting process, which precludes the requirement for subsequent heat treatment of the structure, thereby preserving the initial mechanical properties of the core or base metal.
- the present invention may be applied to produce an all-porous structure using any of the aforementioned metal or metal alloys.
- Such structures can be used as finished product or further processed to form a useful device for either bone or soft tissue in-growth. Additionally, the structure may be used to serve some other function such as that of a lattice to carry cells.
- the pore density, pore size and pore size distribution can be controlled from one location on the structure to another. It is important to note that successive powder layers can differ in porosity by varying factors used for laser scanning powder layers. As for example, a first layer of powder is placed and subsequently scanned. Next a second layer of powder is placed and scanned. In order to control porosity the second scan may be angled relative to the first scan. Additionally, the angling of the scanning as compared to previous and post scans may be maneuvered and changed many times during the process of building a porous structure. If a structure was built without alternating the angling of any subsequent scans you would produce a structure having a plurality of walls rather than one with an interconnecting or non-interconnecting porosity.
- the laser melting process includes scanning the laser beam onto the powder in parallel scan lines with a beam overlap i.e., scan spacing, followed by similar additional scans or subsequent scans at 90°.
- the type of scan chosen may depend on the initial layer thickness as well as the web height required.
- Web height refers to the height of a single stage of the porous structure. The web height may be increased by deposited additional layers of powder of a structure and scanning the laser at the same angle of the previous scan.
- the additional scan lines may be at any angle to the first scan, to form a structure with the formation of a defined porosity, which may be regular or random.
- the scan device may be programmed to proceed in a random generated manner to produce an irregular porous construct but with a defined level of porosity.
- the scan can be pre-programmed using digitized images of various structures, such as a trabecular bone, to produce a similar structure. Contrastingly, the scan may be pre-programmed using the inverse of digitized images, such as the inverse of a digitized trabecular bone to produce trabecular shaped voids.
- Many other scanning strategies are possible, such as a waffle scan, all of which can have interconnecting porosity if required.
- the beam overlap or layer overlap may be achieved by rotation of the laser beam, the part being produced, or a combination of both.
- a first method according to the present invention is intended to produce a porous structure for bone in-growth on the outer surface layer of a prosthesis.
- the nature of the material formed as a result of laser melting of powdered beads is principally dependent on the thermal profile involved (heating rate, soaking time, cooling rate); the condition of the raw material (size and size distribution of powder particles); atmospheric conditions (reducing, inert or oxidizing chamber gas); and accurate control of the deposited layer thickness.
- optimum porosity is between approximately 20% and 40%, and aim to mid value with a mean volume percent of voids of about 70%.
- the preferred pore structure is irregular and interconnected, with a minimum pore size between about 80 ⁇ m and 100 ⁇ m and a maximum pore size between 80 ⁇ m and 800 ⁇ m.
- the structured thickness for in-growth is 1.4-1.6 mm, but can be larger or smaller depending on the application. As for example, it may be necessary to produce even smaller pore sizes for other types of tissue interaction or specific cellular interaction.
- the first phase of development of the present invention involved an investigation, designed to characterize the material transformation process and to identify the optimum parameters for processing using three substrate materials CoCr and Ti stainless steel alloys, with five powder types Ti, CoCr, Ta and Nb, stainless steel.
- FIG. 1 there is shown the apparatus used to carry out the method which comprises an Nd; YAG industrial laser 10 manufactured by Rofin Sinar Lasers, in Hamburg, Germany, integrated to an RSG1014 analogue galvo-scanning head 12 providing a maximum scan speed of 500 mm/s.
- the laser beam 14 is directed into an atmospherically controlled chamber 16 , which consists of two computer-controlled platforms for powder delivery and part building.
- the powder is delivered from a variable capacity chamber 18 into the chamber 16 and is transported by a roller 20 to a build platform 22 above a variable capacity build chamber 24 .
- the build and delivery system parameters are optimized for an even 100 ⁇ m coating of powder to be deposited for every build layer.
- the metals chosen as surface materials are all difficult to process due to their affinity for oxygen. Cr and Ti are easily oxidized when processed by laser in oxygen-containing atmosphere, their oxide products have high melting points and poor flowability. For this reason, and to prevent the formation of other undesirable phases, the methods were carried out under an Argon inert atmosphere in chamber 16 . Pressure remained at or below atmospheric pressure during the entire application.
- the build chamber 24 illustrated in FIG. 1 and method of layering described above is suitable for test specimens and constructs such as three-dimensional freestanding structures.
- an existing device such as acetabular metal shells, hip and knee femoral components, knee tibial components and other such devices, considerable changes to the powder laying technique would need to be applied.
- Co212-e Cobalt Chrome alloy was used.
- the CoCr was configured into square structures, called coupons. Arrays of CoCr coupons were built onto a stainless steel substrate.
- the Co212-e Cobalt Chrome alloy had a particle size distribution of 90 ⁇ 22 um, i.e., 90% of the particles are less than 22 ⁇ m, the composition of which is shown in the table below.
- An array of nine sample coupons were produced as shown in FIG. 2 , with the process of Table 2, using a maximum laser power of 78 watts (W) and laser scanning speed for each coupon varying between 100-260 mms ⁇ 1 .
- W maximum laser power
- a higher laser power may be employed; however, a higher laser power would also necessitate increasing the speed of the laser scan speed in order to produce the desired melting of the powder layer.
- a simple linear x-direction scan was used on each of the coupons. This allowed the processing parameter, beam overlap, to be used to control the space between successive scan lines. That is, with a 100 ⁇ m laser spot size, an overlap of ⁇ 200% produces a 100 ⁇ m gap between scans.
- the acceptable range for the beam overlap is given at +50% to ⁇ 1200% it should be duly noted that the negative number only refers to the fact the there is a gap as opposed to a beam overlap between successive scans. For instance a beam overlap of zero refers to the fact that successive scans on the same layer of powder border each other. If the beam overlap was 5% then 5% of the first scan is overlapped by the second scan. When computing the Andrew number the absolute value of the beam overlap is used. The complete set of process parameters used is shown in Table 2 below.
- CoCr was the first of four powders to be examined and, therefore, a wide range of process parameters was used. In each case, laser power and the pulse repetition rate were kept constant, i.e., continuous laser pulse, to allow the two remaining parameters to be compared. Layer thickness was maintained at 100 ⁇ m throughout all the experiments described here. Layer thickness can, however, vary between 5 ⁇ m to 2000 ⁇ m.
- the particle size description was 80% ⁇ 75 ⁇ m at a purity of 99.85%. Due to its higher melting temperature compared to that of CoCr (Nb being at about 2468° C., and CoCr being at about 1383° C.), the laser parameters used included a reduced scanning speed range and increased beam overlap providing increased specific energy density at the powder bed. In addition, the pulse repetition rate was varied from 20 kHz to 50 kHz.
- Tantalum used in this study had a particular size distribution of 80% ⁇ 75 ⁇ m with a purity of 99.85%.
- Ta has a melting point of about 2996° C. and was processed using the same laser parameters as Nb. Now confident of the atmospheric inertness, the Ta powder was melted directly onto the CoCr and Ti substrates.
- Bio-medical alloys of Titanium were not readily available in powder form and so pure Ti was chosen.
- the particle size distribution for the Ti powder was 80% ⁇ 45 ⁇ m with a purity of 99.58%.
- the same parameters used for Nb and Ta were also used for the Ti powder.
- Ti has a lower melting point than Ta or Nb, Ti being at about 1660° C., but has a higher thermal conductivity than Ta or Nb. This implies that although the powder should require less energy before melting, the improved heat transfer means a larger portion of the energy is conducted away from the melt pool.
- FIG. 5 is an image of two coupons produced from a CoCr array on Ti alloy substrates. This array was chosen because it best satisfied the requirements of this exercise. The parameters were: laser power of 82 W continuous wave (cw); 25% beam overlap; scanning speed varied from 100 mms ⁇ 1 to 260 mms ⁇ 1 in 20 mm ⁇ 1 increments; the images of the coupons shown here, taken from this array, were produced with scanning speeds of 180 mms ⁇ 1 to 200 mms ⁇ 1 .
- the surface is comprised of fused pathways that develop a network of interconnected pores. This structure continues throughout the layer until the interface is reached.
- the interface is characterized by a patchwork of fusion bonds. These bond sites are responsible for securing the interconnected surface structure to the baseplate.
- the macroscopic structure is covered with unmelted powder particles that appear to be loosely attached.
- FIGS. 6 and 7 are the scanning electron microscope images produced from the Nb and Ta coupons on Ti alloy substrates.
- FIGS. 6( a ) to 6 ( e ) are scanning election microscope images of the surface structure of Nb on Ti alloy substrates, produced with a laser power of 82 W cw, ⁇ 40% beam overlap.
- the scanning speeds used were: 160 mms ⁇ 1 for FIG. 6( a ), 190 mms ⁇ 1 for FIG. 6( b ), 200 mms ⁇ 1 for FIG. 6( c ), 210 mms ⁇ 1 for FIG. 6( d ) and 240 mms ⁇ 1 for FIG. 6( e ), respectively.
- FIGS. 7( a ) to 7 ( c ) are scanning election microscope images of the surface structure of Ta on Ti alloy substrates produced using the same parameters used in the Nb or Ti alloy substrates except: FIG. 7( a ) was produced with a scanning speed of 160 mms ⁇ 1 ; FIG. 7( b )'s speed was 200 mms ⁇ 1 and FIG. 7( c )'s speed was 240 mms ⁇ 1 , respectively.
- An increased beam overlap was used here as Nb and Ta have high melting points, which require a greater energy density.
- the surfaces once again exhibit significant levels of unmelted powder particles and loosely attached resolidified beads that vary in size from a few microns to several hundred microns. All samples were loosely brushed after completion and cleaned in an ultrasonic aqueous bath. It is possible that further cleaning measures may reduce the fraction of loose particles.
- FIGS. 8( a ) to 8 ( e ) are scanning electron microscope images taken from the Ti coupons on the CoCr alloy substrates.
- the laser processing parameters used were the same as those for the Nb and Ta powders, with once again only the speed varying.
- the scanning speed was varied from 160 mms ⁇ 1 ( FIG. 8( a ), 170 mms ⁇ 1 ( FIG. 8( b )), 200 mms ⁇ 1 ( FIG. 8( c )); 230 mms ⁇ 1 ( FIG. 8( d ) to 240 mms ⁇ 1 ( FIG. 8( e )).
- the Ti coupon on CoCr samples, FIGS.
- 8( a ) to 8 ( c )) indicate very high density levels compared to the other examples.
- the line-scans can be clearly seen, with good fusion between individual tracks, almost creating a complete surface layer. The surface begins to break up as the scanning speed is increased.
- FIGS. 9( a ) to 9 ( e ) are scanning electron microscope images of surface structures of Ti on Ti alloy substrates produced with the same parameters used in FIGS. 8( a ) to 8 ( e ), respectively. It is unclear why Ti should wet so well on CoCr substrates. In comparison, Ti on Ti exhibits similar characteristic patterns as with Nb, Ta, and CoCr, specifically, an intricate network of interconnected pores.
- the scanning speed, 160 mms ⁇ 1 and the laser power 72 W cw were kept constant while the beam overlaps; ⁇ 400% in FIGS. 10( a ) and 10 ( b ); ⁇ 500% in FIGS. 10( c ) and 10 ( d ) and ⁇ 600% in FIGS. 10( e ) and 10 ( f ), were varied accordingly.
- Scanning electron microscope micrographs, taken from a porous Ti sintered structure provided by Stryker-Howmedica are shown for reference in FIG. 11 .
- the Ti on Ti substrate was sectioned, hot mounted and polished using a process of 1200 and 2500 grade SiC, 6 ⁇ m diamond paste and 70/30 mixture of OPS and 30% H 2 O 2 .
- the polished sample was then etched with 100 ml H 2 O, 5 ml NH.FHF and 2 cm 3 HCl for 30 seconds to bring out the microstructure. Optical images of this sample in section are shown in FIG. 12 .
- FIG. 13 is an image taken from a non-contact surface profilimentry to show the surface structures obtained when using Ti, CoCr, Ta and Nb on Ti substrates. Values for Ra, Rq and Rb roughness are also shown.
- the key laser parameters varied for forming the three-dimensional metallic porous structures are: (a) Laser scanning speed (v.) in (mms ⁇ 1 ), which controls the rate at which the laser traverses the powder bed; (b) Laser power, P(W), which in conjunction with the laser spot size controls the intensity of the laser beam. The spot size was kept constant throughout the experiment; (c) Frequency, (Hz) or pulse repetition rate. This variable controls the number of laser pulses per second. A lower frequency delivers a higher peak power and vice versa.
- the line width can be related to the laser scanning speed and the laser power to provide a measure of specific density, known as the “Andrew Number”, where:
- the Andrew number is the basis for the calculation of the present invention.
- the Andrew number may also be calculated by substituting the line separation (d) for beam width (b).
- the two methods of calculating the Andrew number will result in different values being obtained.
- line separation (d) as a factor only on track of fused powder is considered, whereas when using the beam width (b) as a factor, two tracks of fused powder are considered as well as the relative influence of one track to the next. For this reason we have chosen to concern our with the Andrew number using scan spacing as a calculating factor. It can thus be appreciated, that the closer these tracks are together the greater the influence they have on one another.
- the laser power may be varied between 5 W and 1000 W. Utilizing lower power may be necessary for small and intricate parts but would be economically inefficient for such coatings and structures described herein. It should be noted that the upper limit of laser power is restricted because of the availability of current laser technology. However, if a laser was produced having a power in excess of 1000 W, the scanning speed of the laser could be increased in order that an acceptable Andrew number is achieved. A spot size having a range between 5 um(fix) to 500 um(fix) is also possible. For the spot size to increase while still maintaining an acceptable Andrew number, either the laser power must be increased or the scanning speed decreased.
- the above formula gives an indication of how the physical parameters can vary the quantity of energy absorbed by the powder bed. That is, if the melted powder has limited cohesion, e.g. insufficient melting, the parameters can be varied to concentrate the energy supply to the powder.
- High Andrew numbers result in reduced pore coverage and an increase in pore size due to the effects of increased melt volume and flow.
- Low Andrew numbers result in low melt volume, high pore density and small pores.
- Current satisfactory Andrew numbers are approximately 0.3 J/mm ⁇ 2 to 8 J/mm ⁇ 2 and are applicable to many alternative laser sources. It is possible to use a higher powered laser with increased scanning speed and obtain an Andrew number within the working range stated above.
- FIGS. 4( a ) to 4 ( c ) are scanning election microscope images of the surface structure of CoCr on stainless steel produced with a laser power of 82 W cw.
- FIG. 4( a ) was produced with a laser scanning speed of 105 mms ⁇ 1
- FIG. 4( b ) was produced with a laser scanning speed of 135 mms ⁇ 1 .
- FIG. 4( a ) was produced with a laser scanning speed of 105 mms ⁇ 1
- FIG. 4( b ) was produced with a laser scanning speed of 135 mms ⁇ 1 .
- FIG. 4( c ) is an image of the same structure in FIG. 4( b ), in section. There is a significant self-ordering within the overall structure. Larger columnar structures are selectively built leaving large regions of unmelted powder. It is worth noting that these pillars are around 300 ⁇ m wide, over 1.6 mm tall and fuse well with the substrate, as seen in FIG. 4( c ). Further analysis shows that the use of a hatched scanning format allows porosity to be more sufficiently controlled to allow the pore size to be directly controlled by the beam overlap.
- Increased fusion may, if required, be obtained by heating the substrate, powder or both prior to scanning.
- Such heating sources are commonly included in standard selective laser sintering/melting machines to permit this operation.
- FIG. 26 shows the metallography of the structures with energy dispersive spectroscopy (EDS) revealing the relative metal positions within the build.
- EDS energy dispersive spectroscopy
- a typical waffle build of titanium on a titanium substrate was constructed as a way of regulating the porous structure. Scanning sequences of 0° 0°0°, 90° 90° 90°, 45° 45°45°, 135°, 135°, 135°, of layer thickness 0.1 mm were developed to form a waffle. Three layers of each were necessary to obtain sufficient web thickness in the “z” direction to give a structure of adequate strength. Typical parameters employed were: Laser power was 82 watts, operating frequency between 0 (cw) and 40 KHz, scan speed of between 160 and 240 mm/sec with a beam overlap of ⁇ 700%. FIG. 27 gives an indication of the effect of line spacing and pore size. FIG.
- FIG. 28(a) shows typical examples of the waffle structure.
- the magnification level changes from 10, 20, 30, 70 and 150 times normal viewing as one moves respectively from Fig. (b) to (f).
- FIG. 28(a) more specifically shows Ti powder on a Ti substrate with a controlled porosity by varying line spacing, i.e., beam overlap.
- Trabecular structures of titanium on a titanium substrate were constructed as a way of randomising the porous structures.
- An STL (sterolithography) file representing trabecular structure was produced from a micro CT scan of trabecular bone. This file was sliced and the slice data sent digitally to the scanning control. This allowed the layer-by-layer building of a metallic facsimile to be realised.
- FIG. 29 shows a cross-sectional view of such a construct.
- a method for making lattice-type constructs was referred to in the relevant art.
- a typical example of this type of structure is shown in FIG. 30 .
- the scanning strategy employed to form such a construct was mentioned and such a strategy could be produced within the range of Andrew numbers outlined.
- Table 4 shows an indication of scanning strategies and their relationships to the Andrew number.
- the second and preferred approach uses a continuous scanning strategy whereby the pores are developed by the planar deposition of laser melted powder tracks superimposed over each other. This superimposition combined with the melt flow produces random and pseudorandom porous structures.
- the properties of the final structure, randomness, interconnectivity, mechanical strength and thermal response are controlled by the process parameters employed.
- One set of scanning parameters used was: Scanning sequences of 0° 0°0°, 90° 90° 90°, 45° 45° 45°, 135°, 135°, 135°, 135°, of layer thickness 0.1 mm were developed to form a waffle. Three layers of each were necessary to obtain sufficient web thickness in the “z” direction. The array of sequences was repeated many times to give a construct of the desired height.
- Laser power was 82 watts, operating frequency between 0 (cw) and 40 KHz, scan speed of between 160 and 240 mm/sec with a beam overlap of ⁇ 700%.
- FIG. 32 shows such a construct.
- Laser cleaning or acid etching technique may be effective. Additionally, a rigorous cleaning protocol to remove all loose powder may entail blowing the porous structure with clean dry compressed gas, followed by a period of ultrasonic agitation in a treatment fluid. Once dried, a laser scan may be used to seal any remaining loose particles.
- a typical example of the use of a bond coat is provided by the combination of titanium on to a cobalt chromium substrate. Tantalum also was an effective bond coat in this example. Note that the bond coat may be applied by laser technology, but other methods are also possible such as gas plasma deposition.
- FIGS. 13( a ) to 13 ( d ) show the surface profile.
- the Surface Data shown in FIGS. 14( a ) and 14 ( b ) and 15 ( a ) and 15 ( b ) show a coded profile of the plan views of the samples.
- FIGS. 16 to 25 are scanning electron microscope (SEM) micrographs of a series of single layer Ti on CoCr and Ti on Ti images that were produced prior to the multi-layer builds shown in FIGS. 8 and 9 respectively and as follows.
- the method according to the present invention can produce surface structures on all powder/baseplate combinations with careful selection of process parameters.
- the process is carried out on flat baseplates that provide for easy powder delivery in successive layers of around 100 ⁇ m thickness. Control of powder layer thickness is very important if consistent surface properties are required.
- the application of this technology can also be applied to curved surfaces such as those found in modern prosthetic devices; with refinements being made to the powder layer technique.
- the structures have all received ultrasonic and aqueous cleaning.
- the resultant porous surfaces produced by the Direct Laser Remelting process exhibit small particulates that are scattered throughout the structure. It is unclear at this stage whether these particulates are bonded to the surface or loosely attached but there are means to remove the particulates if required.
- the Direct Laser Remelting process has the ability to produce porous structures that are suitable for bone in-growth applications.
- the powdered surfaces have undergone considerable thermal cycling culminating in rapid cooling rates that have produced very fine dendritic structures (e.g. FIGS. 13( a ) to 13 ( d )).
- the Direct Laser Remelting process can produce effective bone in-growth surfaces and the manufacturing costs are reasonable.
- the object has been to provide a porous structure on a base but the present invention can also be used to provide a non-porous structure on such a base to form a three-dimensional structure.
- the same techniques can be utilized for the materials concerned but the laser processing parameters can be appropriately selected so that a substantially solid non-porous structure is achieved.
- a technique can be used to deposit the powder onto a suitable carrier, for example a mold, and to carry out the process without the use of a base so that a three-dimensional structure is achieved which can be either porous, as described above, or non-porous if required.
- this method can, therefore, be used to produce article from the metals referred to which can be created to a desired shape and which may or may not require subsequent machining. Yet again, such an article can be produced so that it has a graded porosity of, e.g., non-porous through various degrees of porosity to the outer surface layer.
- Such articles could be surgical prostheses, parts or any other article to which this method of production would be advantageous.
Abstract
Description
- This application is a continuation of U.S. application Ser. No. 10/704,270, filed on Nov. 7, 2003, which claims the benefit of U.S. Provisional Application No. 60/424,923 filed on Nov. 8, 2002, and U.S. Provisional Application No. 60/425,657 filed on Nov. 12, 2002, the disclosures of which are incorporated herein by reference.
- The present invention relates to a porous surface and a method for forming the same, which uses a directed energy beam to selectively remelt a powder to produce a part. In particular, this invention relates to a computer-aided laser apparatus, which sequentially remelts a plurality of powder layers to build the designed part in a layer-by-layer fashion. The present application is particularly directed toward a method of forming a porous and partially porous metallic structure.
- The field of free-form fabrication has seen many important recent advances in the fabrication of articles directly from computer controlled databases. These advances, many of which are in the field of rapid prototyping of articles such as prototype parts and mold dies, have greatly reduced the time and expense required to fabricate articles, particularly in contrast to conventional machining processes in which a block of material, such as a metal, is machined according to engineering drawings.
- One example of a modern rapid prototyping technology is the selective laser sintering process practiced by systems available from DTM Corporation of Austin, Tex. According to this technology, articles are produced in layer-wise fashion from a laser-fusible powder that is dispensed one layer at a time. The powder is fused, remelted or sintered, by the application of laser energy that is directed in raster-scan fashion to portions of the powder layer corresponding to a cross section of the article. After the fusing of the powder in each layer, an additional layer of powder is dispensed, and the process repeated, with fused portions or lateral layers fusing so as to fuse portions of previous laid layers until the article is complete. Detailed descriptions of the selective laser sintering technology may be found in U.S. Pat. No. 4,863,538, U.S. Pat. No. 5,017,753, U.S. Pat. No. 5,076,869 and U.S. Pat. No. 4,944,817, all assigned to Board of Regents, the University of Texas. Quasi-porous structures have also been developed in the form of regular and irregular lattice arrangements in which individual elements (column and connecting cross-members) are constructed singularly from a pre-defined computer-aided design model of the external geometry and lattice structure. The selective laser remelting and sintering technologies have enabled the direct manufacture of solid or dense three-dimensional articles of high resolution and dimensional accuracy from a variety of materials including wax, metal powders with binders, polycarbonate, nylon, other plastics and composite materials, such as polymer-coated metals and ceramics.
- The field of the rapid prototyping of parts has, in recent years, made large improvements in broadening high strain, high density, parts for use in the design and pilot production of many useful articles, including metal parts. These advances have permitted the selective laser remelting and sintering processes to now also be used in fabricating prototype tooling for injection molding, with expected tool life in access of ten thousand mold cycles. The technologies have also been applied to the direct fabrication of articles, such as molds, from metal powders without a binder. Examples of metal powder reportedly used in such direct fabrication include two-phase metal powders of the copper-tins, copper-solder (the solder being 70% led and 30% tin), and bronze-nickel systems. The metal articles formed in these ways have been quite dense, for example, having densities of up to 70% to 80% of fully dense (prior to any infiltration). Prior applications of this technology have strived to increase the density of the metal structures formed by the remelting or sintering processes. The field of rapid prototyping of parts has focused on providing high strength, high density, parts for use and design in production of many useful articles, including metal parts.
- However, while the field of rapid prototyping has focused on increasing density of such three-dimensional structures, the field has not focused its attention on reducing the density of three-dimensional structures. Consequently, applications where porous and partially porous metallic structures, and more particularly metal porous structures with interconnected porosity, are advantageous for use have been ignored. It is an object of this invention to use a laser and powder metal to form pores in structures in which pores are irregular in size and have a controlled total porosity. It is a further object to produce porous tissue in growth surfaces with interconnected porosity with uniform pores and porosity.
- The present invention relates to a method for producing a three-dimensional porous structure particularly for use with tissue ingrowth. In one embodiment of the present invention, a layer of metallic powder is deposited onto a substrate or a build platform. Preferred metals for the powder include titanium, titanium alloys, stainless steel, cobalt chrome alloys, tantalum or niobium. A laser beam with predetermined settings scans the powder layer causing the powder to preferentially remelt and consequently solidify with a decreased density, resulting from an increase in porosity as compared to a solid metal. The range of the laser's power may be between 5 W and 1000 W. After the first layer of powder has been completed, successive offset layering and remelting are continued until the porous part has been successfully completed. In this embodiment, the benefit of the part formed is that that decreased density increases porosity thus enabling the part to be used for, among other things, tissue ingrowth.
- In a second embodiment, the first layer of metallic powder is deposited onto a solid base or core and fused thereto. Preferred metals used for the core include titanium, titanium alloys, stainless steel, cobalt chrome alloys, tantalum and niobium. Successive powder layers of the same or different materials are once again added in a layer-by-layer fashion until the part is completed. This embodiment has the desired effect of providing a structure in which the porosity may be increased as the structure is built, resulting in a graded profile in which the mechanical properties will also be reduced outwards from the core. This will allow the formed part to be used for, among other things, medical implants and prosthesis, but yet still include a surface for tissue ingrowth.
- The method of producing a three-dimensional porous tissue ingrowth structure may include depositing a first layer of a powder made from a metal selected from the group consisting of titanium, titanium alloys, stainless steel, cobalt chrome alloys, tantalum and niobium, onto a substrate. Followed by scanning a laser beam at least once over the first layer of powder. The laser beam having a power (P) in Joule per seconds with a scanning speed (v) in millimeters per second with a range between 80 and 400 mms. and a beam overlap (b) in millimeters of between 50% and −1200%. Such that the number calculated by the formula P/(b×v) lies between the range 0.3-8 J/mm2.
- At least one additional layer of powder is deposited and then the laser scanning steps for each successive layer are repeated until a desired web height is reached. In a second embodiment, during the step of repeating the laser scanning steps, at least one laser scan is carried out angled relative to another laser scan in order to develop an interconnecting or non-interconnecting porosity.
- The thickness of the first layer and said successive layers of powder is between 5 μm-2000 μm. The laser can be applied either continuously or in a pulse manner, with the frequency of the pulse being in the range of approximately 1 KHz to 50 KHz. Preferably, the method is carried out under an inert atmosphere, more preferably specifically an Argon inert atmosphere.
- In order to achieve a greater mechanical strength between the base or core and the first layer of powder a third metal may be used to act as an intermediate. The third metal would act as a bond coat between the core and first layer of powder. Additionally the core may be integral with the resultant porous ingrowth structure and impart additional physical properties to the overall construct. The core may also be detachable from the resultant porous surface buildup.
- It is the object of the present invention to provide a method of fabricating porous and partially porous metallic structures with a known porosity for use in particularly but not exclusively hard or soft tissue interlock structures or medical prosthesis.
- These and other objects are accomplished by a process of fabricating an article in which laser-directed techniques are used to produce a porous three-dimensional structure with interconnected porosity and predetermined pore density, pore size and pore-size distribution. The article is fabricated, in the example of remelting, by using a laser and varying either the power of the laser, the layer thickness of the powder, laser beam diameter, scanning speed of the laser or overlap of the beam. In fabricating a three-dimensional structure, the powder can be either applied to a solid base or not. The article is formed in layer-wise fashion until completion.
- Methods of forming the porous surface of the present invention can be performed in many ways and some embodiments will now be described by way of example and with reference to the accompanying drawings in which:
-
FIG. 1 is a diagrammatic illustration of the apparatus used to make test samples according to the processes of the present invention; -
FIG. 2 is a photographic image showing an array of samples produced by the processes as performed by the apparatus ofFIG. 1 ; -
FIG. 3 is a table showing a series of parameters used for the samples ofFIG. 2 ; -
FIGS. 4 to 10 are scanning electron microscope images of the surface structure of various samples made by the method according to the invention; -
FIG. 11 is a scanning electron microscope micrograph taken from a porous Ti sintered structure; -
FIG. 12 is an optical image of a section through a sample showing the microstructure; -
FIG. 13 is an image detailing surface structures; -
FIGS. 14 and 15 are non-contact surface profilimetry images detailing plan views of the samples; and -
FIGS. 16 to 25 are scanning electron microscope micrographs produced prior to multi-layer builds shown inFIGS. 7 and 8 . -
FIG. 26 indicates the metallography and spectra of a typical bond coat structure. -
FIG. 27 shows the effect of line spacing on pore size. -
FIG. 28 a-f are examples of typical waffle structures. -
FIG. 29 is a trabecular bone-type structure constructed from a micro CT scan. -
FIG. 30 shows typical freestanding structures. -
FIG. 31 shows a freestanding structure built using the preferred scanning strategy. - The present invention relates to a method of forming porous and partially porous metallic structures which are particularly but not exclusively applicable for use in hard or soft tissue interlock structures for medical implants and prosthesis. The method makes use of laser technology by employing a variety of scanning strategies. Typical metal and metal alloys employed include stainless steel, cobalt chromium alloys, titanium and its alloys, tantalum and niobium, all of which have been used in medical device applications. The present invention can be used for such medical device applications where bone and soft tissue interlock with a component is required, or where a controlled structure is required to more closely match the mechanical properties of the device with surrounding tissue. Additionally, the present invention may be employed to enhance the biocompatibility of a porous structure with animal tissue. With these advantages in mind, a structure may be created using specific dimensions required to accommodate a particular patient.
- One particular intention of the present invention is to produce a three-dimensional structure using a direct laser remelt process, for example, for building structures with or without a solid base or core. When applied to an orthopedic prosthesis, the three-dimensional structure could be used to provide a porous outer layer to form a bone in-growth structure. Alternatively, the porous structure, when applied to a core, could be used to form a prosthesis with a defined stiffness to both fulfill the requirement of a modulus match with surrounding tissue and provide interconnected porosity for tissue interlock. A further use could be to form an all-porous structure with grade pore size to interact with more than one type of tissue. Again, the process can be used to build on a solid base or core with an outer porous surface, the porosity of which is constant or which varies. The base or core materials to which the process is applied is either titanium and its alloys, stainless steel, cobalt chrome alloys, tantalum or niobium. The preferred surface coatings are titanium, cobalt chrome and tantalum but both stainless steel and niobium can also be used. Fully porous structures may be built from any of the materials tested, with the preferred material being titanium. One intention of the present invention is to produce a method which can be exploited on a commercial basis for the production of, for example, bone interlock surfaces on a device although it has many other uses.
- According to the present invention, a method of forming a three-dimensional structure includes building the shape by laser melting powdered titanium and titanium alloys, stainless steel, cobalt chrome alloys, tantalum or niobium. The laser may be a continuous wave or pulsed laser beam.
- The method can be performed so that the structure is porous and if desired, the pores can be interconnecting to provide an interconnected porosity.
- If desired, the method can include using a base or core of cobalt chrome alloy, titanium or alloy, stainless steel, niobium and tantalum, on which to build a porous layer of any one of the aforementioned metals and alloys by laser melting using a continuous or pulsed laser beam. Thus, a mixture of desired mixed materials may be employed.
- Thus, the method can be applied to an existing article made from cobalt chrome, titanium or titanium alloys, stainless steel, tantalum or niobium, such as an orthopedic implant, to produce a porous outer layer from any of the aforementioned metals or alloys to provide a bone in-growth structure.
- Preferably, prior to the deposition of any powder onto a substrate, a cleaning operation to ensure a contaminant-free surface may be employed. Typically, this process may include a solvent wash followed by a cleaning scan of the laser beam without the presence of particles.
- In order to increase the mechanical bond between a substrate i.e., core or base, and a first layer of deposited powder a coating process may be employed. The coating process includes applying a third metal directly to the substrate, which has a higher bond strength to the substrate then does the first layer of powder. This process is particularly useful when the substrate and first powder layer are of different materials. The process of coating the substrate may be accomplished using known processes including laser deposition, plasma coating, cold gas dynamic spraying or similar techniques. One example of the coating process includes using either niobium or tantalum as an interface between a cobalt chrome alloy substrate and a first layer of titanium powder.
- The present invention can also include a laser melting process, which precludes the requirement for subsequent heat treatment of the structure, thereby preserving the initial mechanical properties of the core or base metal.
- The present invention may be applied to produce an all-porous structure using any of the aforementioned metal or metal alloys. Such structures can be used as finished product or further processed to form a useful device for either bone or soft tissue in-growth. Additionally, the structure may be used to serve some other function such as that of a lattice to carry cells.
- The pore density, pore size and pore size distribution can be controlled from one location on the structure to another. It is important to note that successive powder layers can differ in porosity by varying factors used for laser scanning powder layers. As for example, a first layer of powder is placed and subsequently scanned. Next a second layer of powder is placed and scanned. In order to control porosity the second scan may be angled relative to the first scan. Additionally, the angling of the scanning as compared to previous and post scans may be maneuvered and changed many times during the process of building a porous structure. If a structure was built without alternating the angling of any subsequent scans you would produce a structure having a plurality of walls rather than one with an interconnecting or non-interconnecting porosity.
- In one such method, the laser melting process includes scanning the laser beam onto the powder in parallel scan lines with a beam overlap i.e., scan spacing, followed by similar additional scans or subsequent scans at 90°. The type of scan chosen may depend on the initial layer thickness as well as the web height required. Web height refers to the height of a single stage of the porous structure. The web height may be increased by deposited additional layers of powder of a structure and scanning the laser at the same angle of the previous scan.
- Further, the additional scan lines may be at any angle to the first scan, to form a structure with the formation of a defined porosity, which may be regular or random. The scan device may be programmed to proceed in a random generated manner to produce an irregular porous construct but with a defined level of porosity. Furthermore, the scan can be pre-programmed using digitized images of various structures, such as a trabecular bone, to produce a similar structure. Contrastingly, the scan may be pre-programmed using the inverse of digitized images, such as the inverse of a digitized trabecular bone to produce trabecular shaped voids. Many other scanning strategies are possible, such as a waffle scan, all of which can have interconnecting porosity if required.
- The beam overlap or layer overlap may be achieved by rotation of the laser beam, the part being produced, or a combination of both.
- A first method according to the present invention is intended to produce a porous structure for bone in-growth on the outer surface layer of a prosthesis.
- To produce a porous surface structure, the nature of the material formed as a result of laser melting of powdered beads is principally dependent on the thermal profile involved (heating rate, soaking time, cooling rate); the condition of the raw material (size and size distribution of powder particles); atmospheric conditions (reducing, inert or oxidizing chamber gas); and accurate control of the deposited layer thickness.
- There have been a number of studies to determine the optimum pore structure for maximization of bone in-growth on prostheses. The general findings suggest that optimum porosity is between approximately 20% and 40%, and aim to mid value with a mean volume percent of voids of about 70%. The preferred pore structure is irregular and interconnected, with a minimum pore size between about 80 μm and 100 μm and a maximum pore size between 80 μm and 800 μm. The structured thickness for in-growth is 1.4-1.6 mm, but can be larger or smaller depending on the application. As for example, it may be necessary to produce even smaller pore sizes for other types of tissue interaction or specific cellular interaction.
- The first phase of development of the present invention involved an investigation, designed to characterize the material transformation process and to identify the optimum parameters for processing using three substrate materials CoCr and Ti stainless steel alloys, with five powder types Ti, CoCr, Ta and Nb, stainless steel.
- The initial Direct Laser Remelting trials explored a comprehensive range of process parameters during the production of a number of coated base substrates. Results from this task were evaluated using laser scanning and white light interferometry in order to define the range of process parameters that produced the optimum pore structure.
- Referring to
FIG. 1 , there is shown the apparatus used to carry out the method which comprises an Nd; YAGindustrial laser 10 manufactured by Rofin Sinar Lasers, in Hamburg, Germany, integrated to an RSG1014 analogue galvo-scanning head 12 providing a maximum scan speed of 500 mm/s. The laser beam 14 is directed into an atmospherically controlled chamber 16, which consists of two computer-controlled platforms for powder delivery and part building. The powder is delivered from a variable capacity chamber 18 into the chamber 16 and is transported by aroller 20 to a build platform 22 above a variable capacity build chamber 24. In the embodiment shown inFIG. 1 , the build and delivery system parameters are optimized for an even 100 μm coating of powder to be deposited for every build layer. The metals chosen as surface materials are all difficult to process due to their affinity for oxygen. Cr and Ti are easily oxidized when processed by laser in oxygen-containing atmosphere, their oxide products have high melting points and poor flowability. For this reason, and to prevent the formation of other undesirable phases, the methods were carried out under an Argon inert atmosphere in chamber 16. Pressure remained at or below atmospheric pressure during the entire application. - The build chamber 24 illustrated in
FIG. 1 and method of layering described above is suitable for test specimens and constructs such as three-dimensional freestanding structures. However, in order to build on to an existing device, such as acetabular metal shells, hip and knee femoral components, knee tibial components and other such devices, considerable changes to the powder laying technique would need to be applied. - Preliminary experiments were performed on CoCr alloy to determine the efficacy of in-situ laser cleaning of the substrate. Typical processing conditions were: Laser power of 82 W, pulse frequency of 30 KHz, and a laser scan speed of 160 mm/sec.
- Preliminary experiments were performed on CoCr to assess the environment conditions within the chamber. In these examples, Co212-e Cobalt Chrome alloy was used. The CoCr was configured into square structures, called coupons. Arrays of CoCr coupons were built onto a stainless steel substrate. The Co212-e Cobalt Chrome alloy had a particle size distribution of 90<22 um, i.e., 90% of the particles are less than 22 μm, the composition of which is shown in the table below.
-
TABLE 1 Composition of Co212-e CoCr alloy Element Cr Mo Si Fe Mn Ni N C Co Wt % 27.1 5.9 0.84 0.55 0.21 0.20 0.16 0.050 Balance - An array of nine sample coupons were produced as shown in
FIG. 2 , with the process of Table 2, using a maximum laser power of 78 watts (W) and laser scanning speed for each coupon varying between 100-260 mms−1. Of course a higher laser power may be employed; however, a higher laser power would also necessitate increasing the speed of the laser scan speed in order to produce the desired melting of the powder layer. A simple linear x-direction scan was used on each of the coupons. This allowed the processing parameter, beam overlap, to be used to control the space between successive scan lines. That is, with a 100 μm laser spot size, an overlap of −200% produces a 100 μm gap between scans. Although the acceptable range for the beam overlap is given at +50% to −1200% it should be duly noted that the negative number only refers to the fact the there is a gap as opposed to a beam overlap between successive scans. For instance a beam overlap of zero refers to the fact that successive scans on the same layer of powder border each other. If the beam overlap was 5% then 5% of the first scan is overlapped by the second scan. When computing the Andrew number the absolute value of the beam overlap is used. The complete set of process parameters used is shown in Table 2 below. -
TABLE 2 Process parameters Power Layer Beam Scanning Overlap Watts Thickness Diameter Speed No. of (% of line (W) (μm) (μm) (mms−1) Atmosphere Layers width) 78 100 100 100-260 No 16 25, 50, −500 - The incremental changes in scanning speed and the size of the speed range were modified as the experiments progressed. To begin with, a large range of speeds was used to provide an initial indication of the material's performance and the propensity to melt. As the experiments progressed, the range was reduced to more closely define the process window. Speed and beam overlap variations were used to modify the specific energy density being applied to the powder bed and change the characteristics of the final structure. The complete series of parameters are given in
FIG. 3 , the parameters sets used for the definitive samples are shaded in gray. - CoCr was the first of four powders to be examined and, therefore, a wide range of process parameters was used. In each case, laser power and the pulse repetition rate were kept constant, i.e., continuous laser pulse, to allow the two remaining parameters to be compared. Layer thickness was maintained at 100 μm throughout all the experiments described here. Layer thickness can, however, vary between 5 μm to 2000 μm.
- On completion of the initial series of experiments using CoCr powder on 2.5 mm thick stainless steel substrates, basic optical analysis was conducted of the surface of the coupons to ascertain the size of the pores and degree of porosity being obtained. Once a desired pore size was obtained and the coupons had suitable cohesion, the two experiments closest to the optimum desired pore size were repeated using first CoCr and then Ti substrates. The same structure could be obtained by other parameters.
- Following the conclusion of the CoCr experiments, the remaining three powders; Niobium, Tantalum and Titanium were investigated in turn. The procedure followed a simple course although fewer parameter sets were explored as the higher melting points of these materials forced the reduction in speeds compared to CoCr powder.
- For Niobium, the particle size description was 80%<75 μm at a purity of 99.85%. Due to its higher melting temperature compared to that of CoCr (Nb being at about 2468° C., and CoCr being at about 1383° C.), the laser parameters used included a reduced scanning speed range and increased beam overlap providing increased specific energy density at the powder bed. In addition, the pulse repetition rate was varied from 20 kHz to 50 kHz.
- On completion of a small number (four in total) of preliminary experiments of Nb on stainless steel substrate, the experiment with the most ideal parameters was repeated on both the CoCr and Ti substrates.
- The Tantalum used in this study had a particular size distribution of 80%<75 μm with a purity of 99.85%. Ta has a melting point of about 2996° C. and was processed using the same laser parameters as Nb. Now confident of the atmospheric inertness, the Ta powder was melted directly onto the CoCr and Ti substrates.
- Bio-medical alloys of Titanium were not readily available in powder form and so pure Ti was chosen. The particle size distribution for the Ti powder was 80%<45 μm with a purity of 99.58%. The same parameters used for Nb and Ta were also used for the Ti powder. Ti has a lower melting point than Ta or Nb, Ti being at about 1660° C., but has a higher thermal conductivity than Ta or Nb. This implies that although the powder should require less energy before melting, the improved heat transfer means a larger portion of the energy is conducted away from the melt pool.
- Following the completion of samples with all four powders on the required substrates, surface analysis was conducted using optical analysis and a scanning electron microscope to obtain images of the resultant pores. Porosity was calculated using a simple image processing technique involving the setting of contrast thresholds and pixel counting. While this technique is not the most accurate method, it allows the rapid analysis of small samples produced. Techniques such as Xylene impregnation would yield more accurate results but they are time consuming and require larger samples than those produced here.
- Following an extended series of experimentation, two sets of laser processing parameters were selected for the laser melting of CoCr powder. From analysis of the stainless steel substrates, it was seen that a large portion of the results fell within the pore size required for these materials, stated as being in the range of 80 μm to 400 μm.
- Optical analysis of the surface structure of each of the coupons produced with CoCr on CoCr and Ti alloy substrates were initially viewed but due to problems with the depth of field associated with an optical microscope, little information could be extracted. In addition to the coupons that were produced to satisfy the project requirements, two experiments were conducted using a relatively large negative beam overlap of −250 and −500%. Optical images of the coupon's surface and in section are shown in
FIG. 4 . These were not the definitive parameters chosen for the final arrays on CoCr and Ti alloy substrates as the pore size exceeds the required 80 μm to 400 μm. They are shown here to display what the Direct Laser Remelting process can produce when an excessive beam overlap is used. - To provide a clearer indication of the pore size and pore density, the optical analysis was repeated using images obtained from the scanning electron microscope.
FIG. 5 is an image of two coupons produced from a CoCr array on Ti alloy substrates. This array was chosen because it best satisfied the requirements of this exercise. The parameters were: laser power of 82 W continuous wave (cw); 25% beam overlap; scanning speed varied from 100 mms−1 to 260 mms−1 in 20 mm−1 increments; the images of the coupons shown here, taken from this array, were produced with scanning speeds of 180 mms−1 to 200 mms−1. The surface is comprised of fused pathways that develop a network of interconnected pores. This structure continues throughout the layer until the interface is reached. The interface is characterized by a patchwork of fusion bonds. These bond sites are responsible for securing the interconnected surface structure to the baseplate. The macroscopic structure is covered with unmelted powder particles that appear to be loosely attached. In addition, there are larger resolidified globules that may have limited bonding to the surface. -
FIGS. 6 and 7 are the scanning electron microscope images produced from the Nb and Ta coupons on Ti alloy substrates. Specifically,FIGS. 6( a) to 6(e) are scanning election microscope images of the surface structure of Nb on Ti alloy substrates, produced with a laser power of 82 W cw, −40% beam overlap. The scanning speeds used were: 160 mms−1 forFIG. 6( a), 190 mms−1 forFIG. 6( b), 200 mms−1 forFIG. 6( c), 210 mms−1 forFIG. 6( d) and 240 mms−1 forFIG. 6( e), respectively. -
FIGS. 7( a) to 7(c) are scanning election microscope images of the surface structure of Ta on Ti alloy substrates produced using the same parameters used in the Nb or Ti alloy substrates except:FIG. 7( a) was produced with a scanning speed of 160 mms−1;FIG. 7( b)'s speed was 200 mms−1 andFIG. 7( c)'s speed was 240 mms−1, respectively. An increased beam overlap was used here as Nb and Ta have high melting points, which require a greater energy density. The surfaces once again exhibit significant levels of unmelted powder particles and loosely attached resolidified beads that vary in size from a few microns to several hundred microns. All samples were loosely brushed after completion and cleaned in an ultrasonic aqueous bath. It is possible that further cleaning measures may reduce the fraction of loose particles. -
FIGS. 8( a) to 8(e) are scanning electron microscope images taken from the Ti coupons on the CoCr alloy substrates. The laser processing parameters used were the same as those for the Nb and Ta powders, with once again only the speed varying. The scanning speed was varied from 160 mms−1 (FIG. 8( a), 170 mms−1 (FIG. 8( b)), 200 mms−1 (FIG. 8( c)); 230 mms−1 (FIG. 8( d) to 240 mms−1 (FIG. 8( e)). The Ti coupon on CoCr samples, (FIGS. 8( a) to 8(c)) indicate very high density levels compared to the other examples. The line-scans can be clearly seen, with good fusion between individual tracks, almost creating a complete surface layer. The surface begins to break up as the scanning speed is increased. -
FIGS. 9( a) to 9(e) are scanning electron microscope images of surface structures of Ti on Ti alloy substrates produced with the same parameters used inFIGS. 8( a) to 8(e), respectively. It is unclear why Ti should wet so well on CoCr substrates. In comparison, Ti on Ti exhibits similar characteristic patterns as with Nb, Ta, and CoCr, specifically, an intricate network of interconnected pores. - Following the completion of the multi-layer coupons, a series of 20 mm×20 mm structures were produced from Ti that utilized an X and Y-direction “waffle” scanning format using the optimum Ti operating parameters with the two scans being orthogonal to one another. The intention behind these experiments was to demonstrate the ability of the Direct Laser Remelting process to produce parts with a controlled porosity, e.g. internal channels of dimensions equal to the required pore size, e.g. 80 μm to 400 μm. To do this, a relatively large beam overlap of between −400% and −600% was used. Scanning electron microscope images of the surfaces of these structures are shown in
FIGS. 10( a) to 10(f). The scanning speed, 160 mms−1 and the laser power 72 W cw were kept constant while the beam overlaps; −400% inFIGS. 10( a) and 10(b); −500% inFIGS. 10( c) and 10(d) and −600% inFIGS. 10( e) and 10(f), were varied accordingly. Scanning electron microscope micrographs, taken from a porous Ti sintered structure provided by Stryker-Howmedica are shown for reference inFIG. 11 . - To illustrate more clearly the interaction between the substrate/structure metallurgical interaction, the Ti on Ti substrate was sectioned, hot mounted and polished using a process of 1200 and 2500 grade SiC, 6 μm diamond paste and 70/30 mixture of OPS and 30% H2O2. The polished sample was then etched with 100 ml H2O, 5 ml NH.FHF and 2 cm3 HCl for 30 seconds to bring out the microstructure. Optical images of this sample in section are shown in
FIG. 12 . -
FIG. 13 is an image taken from a non-contact surface profilimentry to show the surface structures obtained when using Ti, CoCr, Ta and Nb on Ti substrates. Values for Ra, Rq and Rb roughness are also shown. - From the optical and scanning election microscope analysis conducted, it is apparent that the Direct Laser Remelting process is capable of satisfying the requirements for pore characteristics, concerning maximum and minimum pore size, interconnectivity and pore density. From the initial visual analysis of the CoCr coupons, it was apparent from these and other examples, that subtle variations in pore structure and coverage could be controlled by scanning velocity and line spacing.
- The key laser parameters varied for forming the three-dimensional metallic porous structures are: (a) Laser scanning speed (v.) in (mms−1), which controls the rate at which the laser traverses the powder bed; (b) Laser power, P(W), which in conjunction with the laser spot size controls the intensity of the laser beam. The spot size was kept constant throughout the experiment; (c) Frequency, (Hz) or pulse repetition rate. This variable controls the number of laser pulses per second. A lower frequency delivers a higher peak power and vice versa.
- The line width can be related to the laser scanning speed and the laser power to provide a measure of specific density, known as the “Andrew Number”, where:
-
- Where P denotes the power of the laser, v is the laser scanning speed and b denotes beam width of the laser. The Andrew number is the basis for the calculation of the present invention. The Andrew number may also be calculated by substituting the line separation (d) for beam width (b). The two methods of calculating the Andrew number will result in different values being obtained. When using line separation (d) as a factor only on track of fused powder is considered, whereas when using the beam width (b) as a factor, two tracks of fused powder are considered as well as the relative influence of one track to the next. For this reason we have chosen to concern ourselves with the Andrew number using scan spacing as a calculating factor. It can thus be appreciated, that the closer these tracks are together the greater the influence they have on one another.
- Additionally, the laser power may be varied between 5 W and 1000 W. Utilizing lower power may be necessary for small and intricate parts but would be economically inefficient for such coatings and structures described herein. It should be noted that the upper limit of laser power is restricted because of the availability of current laser technology. However, if a laser was produced having a power in excess of 1000 W, the scanning speed of the laser could be increased in order that an acceptable Andrew number is achieved. A spot size having a range between 5 um(fix) to 500 um(fix) is also possible. For the spot size to increase while still maintaining an acceptable Andrew number, either the laser power must be increased or the scanning speed decreased.
- The above formula gives an indication of how the physical parameters can vary the quantity of energy absorbed by the powder bed. That is, if the melted powder has limited cohesion, e.g. insufficient melting, the parameters can be varied to concentrate the energy supply to the powder. High Andrew numbers result in reduced pore coverage and an increase in pore size due to the effects of increased melt volume and flow. Low Andrew numbers result in low melt volume, high pore density and small pores. Current satisfactory Andrew numbers are approximately 0.3 J/mm−2 to 8 J/mm−2 and are applicable to many alternative laser sources. It is possible to use a higher powered laser with increased scanning speed and obtain an Andrew number within the working range stated above.
- Line spacing or beam overlap can also be varied to allow for a gap between successive scan lines. It is, therefore, possible to heat selected areas. This gap would allow for a smaller or larger pore size to result. The best illustration of this is shown in
FIGS. 4( a) to 4(c) where a −500% beam overlap has been applied.FIGS. 4( a) to 4(c) are scanning election microscope images of the surface structure of CoCr on stainless steel produced with a laser power of 82 W cw.FIG. 4( a) was produced with a laser scanning speed of 105 mms−1 andFIG. 4( b) was produced with a laser scanning speed of 135 mms−1.FIG. 4( c) is an image of the same structure inFIG. 4( b), in section. There is a significant self-ordering within the overall structure. Larger columnar structures are selectively built leaving large regions of unmelted powder. It is worth noting that these pillars are around 300 μm wide, over 1.6 mm tall and fuse well with the substrate, as seen inFIG. 4( c). Further analysis shows that the use of a hatched scanning format allows porosity to be more sufficiently controlled to allow the pore size to be directly controlled by the beam overlap. - The use of an optical inspection method to determine this approximate porosity is appropriate given the sample size. This method, although not accurate due to the filter selection process, can, if used carefully, provide an indication of porosity. An average porosity level of around 25% was predicted. This porosity level falls within the range of the desired porosity for bone in-growth structures. The mechanical characteristics of the porous structures are determined by the extent of porosity and the interconnecting webs. A balance of these variables is necessary to achieve the mechanical properties required by the intended application.
- Increased fusion may, if required, be obtained by heating the substrate, powder or both prior to scanning. Such heating sources are commonly included in standard selective laser sintering/melting machines to permit this operation.
- Following trials on the titanium build on the cobalt chromium substrate, it was determined that the interface strength was insufficient to serve the intended application. Trials were made by providing a bond coat of either tantalum or niobium on the cobalt chromium substrate prior to the deposition of the titanium layers to for the porous build. The typical protocol involved:
-
- (i) Initial cleaning scan with a scan speed between 60 to 300 mm/sec, laser power 82 watts, frequency of 30 KHz, and a 50% beam overlap.
- (ii) Niobium or tantalum deposition with three layers of 50 μm using a laser power of 82 watts, frequency 30 to 40 KHz, with a laser speed of between 160 to 300 mm/sec. The beam overlap was low at 50% to give good coverage.
- (iii) A build of porous titanium was constructed using a laser power of 82 watts, frequency between 0 (cw) and 40 KHz, scanning speed of between 160 and 240 mm/sec, and beam overlap of −700%.
The strengths of the constructs are indicated in Table 3 with a comparison of the values obtained without the base coat.
-
TABLE 3 MAXIMUM TENSILE LOAD STRENGTH SPECIMEN (kN) (MPa) FAILURE MODE Ti on CoCr 2.5 5 Interface Ti on CoCr 3.1 6.2 Interface 1 (Nb on 13.0 26.18 65% adhesive, 35% bond Co—Cr) interface 4 (Ti on Nb 7.76 15.62 Mostly bond coat on Co—Cr) interface 5 (Ti on Nb 9.24 18.53 20% adhesive, 40% bond on Co—Cr) coat, 40% porous Ti 6 (Ti on Ta 11.58 23.33 Mostly adhesive with on Co—Cr) discrete webbing weakness 8 (Ta on 13.93 27.92 60% adhesive, 40% bond Co—Cr) interface 9 (Ti on Ta 6.76 13.62 100% bond interface on Co—Cr)
FIG. 26 shows the metallography of the structures with energy dispersive spectroscopy (EDS) revealing the relative metal positions within the build. - A typical waffle build of titanium on a titanium substrate was constructed as a way of regulating the porous structure. Scanning sequences of 0° 0°0°, 90° 90° 90°, 45° 45°45°, 135°, 135°, 135°, of layer thickness 0.1 mm were developed to form a waffle. Three layers of each were necessary to obtain sufficient web thickness in the “z” direction to give a structure of adequate strength. Typical parameters employed were: Laser power was 82 watts, operating frequency between 0 (cw) and 40 KHz, scan speed of between 160 and 240 mm/sec with a beam overlap of −700%.
FIG. 27 gives an indication of the effect of line spacing and pore size.FIG. 28(a) shows typical examples of the waffle structure. The magnification level changes from 10, 20, 30, 70 and 150 times normal viewing as one moves respectively from Fig. (b) to (f).FIG. 28(a) more specifically shows Ti powder on a Ti substrate with a controlled porosity by varying line spacing, i.e., beam overlap. - Trabecular structures of titanium on a titanium substrate were constructed as a way of randomising the porous structures. An STL (sterolithography) file representing trabecular structure was produced from a micro CT scan of trabecular bone. This file was sliced and the slice data sent digitally to the scanning control. This allowed the layer-by-layer building of a metallic facsimile to be realised.
FIG. 29 shows a cross-sectional view of such a construct. - A method for making lattice-type constructs was referred to in the relevant art. A typical example of this type of structure is shown in
FIG. 30 . The scanning strategy employed to form such a construct was mentioned and such a strategy could be produced within the range of Andrew numbers outlined. Table 4 shows an indication of scanning strategies and their relationships to the Andrew number. -
TABLE 4 RELATIVE BUILD SCAN PARAMETER LAYER PLATFORM LAYER STRATEGY SET THICKNESS POSITION ADDITIONAL Ti on Ta on CoCr Experimental Procedure. Initial Tantalum Coating Zero 0 Distance Between Roller & Build Platform 0 1st layer 50 μm −50 μm thickness set using feeler gauges but powder not laid in preparation for cleaning scan with no powder. 1 50% Beam P = 82 W Initial Overlap Qs = 30 kHz Cleaning v = 60 mm/s Scan (no An = powder) 27.333 J/mm2 Circular P = 82 W Powder profile. 5 Qs = 40 kHz laid as concentric V = usual circles, 160 mm/s 0.1 mm An = offset to 5.125 J/mm2 negate effects of ‘First Pulse’ 50% Beam P = 82 W Scanned on Overlap Qs = 30 kHz same v = powder 300 mm/s layer as An = previous 5.467 J/mm2 profile scan. 2 Circular P = 82 W 50 μm −100 μm Powder profile. 5 Qs = 40 kHz laid as concentric V = usual circles, 160 mm/s 0.1 mm An = offset to 5.125 J/mm2 negate effects of ‘First Pulse’ 50% Beam P = 82 W Scanned on Overlap Qs = 30 kHz same v = powder 300 mm/s layer as An = previous 5.467 J/mm2 profile scan. 3 Circular P = 82 W 50 μm −150 μm Powder profile. 5 Qs = 40 kHz laid as concentric V = usual circles, 160 mm/s 0.1 mm An = offset to 5.125 J/mm2 negate effects of ‘First Pulse’ 50% Beam P = 82 W Scanned on Overlap Qs = 30 kHz same v = powder 300 mm/s layer as An = previous 5.467 J/mm2 profile scan. Final Titanium Coating 0 1st layer −150 μm thickness set using feeler gauges but powder not laid in preparation for cleaning scan with no powder. 1 50% Beam P = 82 W 50 μm −200 μm Cleaning Overlap Qs = Scan (No 30 kHz powder. v = 60 mm/s An = 27.3 J/mm2 Circular P = 82 W Powder profile. Qs = spread but 5 concentric 40 kHz build circles, V = platform 0.1 mm offset 160 mm/s not to negate An = lowered. effects of 5.125 J/mm2 ‘First Pulse’ 50% Beam P = 82 W Scanned on Overlap Qs = same 30 kHz powder v = layer as 300 mm/s previous An = profile 5.467/mm2 scan. 2 Circular P = 82 W 100 μm −300 μm Powder profile. Qs = laid as 5 concentric 40 kHz usual circles, V = 0.1 mm offset 160 mm/s to negate An = effects of 5.125 J/mm2 ‘First Pulse’ 25% Beam P = 82 W Scanned on Overlap Qs = same 30 kHz powder v = layer as 300 mm/s previous An = profile 3.644 J/mm2 scan. 3 Circular P = 82 W 100 μm −400 μm Powder profile. Qs = laid as 5 concentric 40 kHz usual circles, V = 0.1 mm offset 160 mm/s to negate An = effects of 5.125 J/mm2 ‘First Pulse’ 0% Beam P = 82 W Scanned on Overlap Qs = same 30 kHz powder v = layer as 300 mm/s previous An = profile 2.733 J/mm2 scan. 4 Waffle 0 and P = 82 W 75 μm −475 μm Powder 90° Qs = 0 Hz laid as 700 μm (cw) usual linespacing v = (−600% Beam 240 mm/s overlap) An = 0.488 J/mm2 5 Waffle 0 and P = 82 W 75 μm −550 μm Powder 90° Qs = 0 Hz laid as 700 μm (cw) usual linespacing v = (−600% Beam 240 mm/s overlap) An = 0.488 J/mm2 6 Waffle 0 and P = 82 W 75 μm −625 μm Powder 90° Qs = 0 Hz laid as 700 μm (cw) usual linespacing v = (−600% Beam 240 mm/s overlap) An = 0.488 J/mm2 7 Waffle 45 P = 82 W 75 μm −700 μm Powder and 135° Qs = 0 Hz laid as 700 μm (cw) usual linespacing v = (−600% Beam 240 mm/s overlap) An = 0.488 J/mm2 8 Waffle 45 P = 82 W 75 μm −775 μm Powder and 135° Qs = 0 Hz laid as 700 μm (cw) usual linespacing v = (−600% Beam 240 mm/s overlap) An = 0.488 J/mm2 9 Waffle 45 P = 82 W 75 μm −850 μm Powder and 135° Qs = 0 Hz laid as 700 μm (cw) usual linespacing v = (−600% Beam 240 mm/s overlap) An = 0.488 J/mm2 Ti on Ti Experimental Procedure. Initial Titanium Coating Zero 0 Distance Between Roller & Build Platform 0 1st layer 50 μm −50 μm thickness set using feeler gauges but powder not laid in preparation for cleaning scan with no powder. 1 50% Beam P = 82 W Initial Overlap Qs = 30 kHz Cleaning v = 60 mm/s Scan (no An = powder) 27.333 J/mm2 Circular P = 82 W Powder profile. 5 Qs = 40 kHz laid as concentric V = usual circles, 160 mm/s 0.1 mm An = offset to 5.125 J/mm2 negate effects of ‘First Pulse’ 50% Beam P = 82 W Scanned on Overlap Qs = 30 kHz same v = powder 300 mm/s layer as An = previous 5.467 J/mm2 profile scan. 2 Circular P = 82 W 50 μm −100 μm Powder profile. 5 Qs = 40 kHz laid as concentric V = usual circles, 160 mm/s 0.1 mm An = offset to 5.125 J/mm2 negate effects of ‘First Pulse’ 50% Beam P = 82 W Scanned on Overlap Qs = 30 kHz same v = powder 300 mm/s layer as An = previous 5.467 J/mm2 profile scan. 3 Circular P = 82 W 50 μm −150 μm Powder profile. 5 Qs = 40 kHz laid as concentric V = usual circles, 160 mm/s 0.1 mm An = offset to 5.125 J/mm2 negate effects of ‘First Pulse’ 50% Beam P = 82 W Scanned on Overlap Qs = 30 kHz same v = powder 300 mm/s layer as An = previous 5.467 J/mm2 profile scan. Final Titanium Coating 1 Circular P = 82 W 100 μm −250 μm Powder profile. Qs = 40 kHz laid as 5 concentric V = usual circles, 160 mm/s 0.1 mm offset An = to negate 5.125 J/mm2 effects of ‘First Pulse’ 50% Beam P = 82 W Scanned on Overlap Qs = 30 kHz same v = powder 300 mm/s layer as An = previous 5.467 J/mm2 profile scan 2 Circular P = 82 W 100 μm −350 μm Powder profile. Qs = 40 kHz laid as 5 concentric V = usual circles, 160 mm/s 0.1 mm offset An = to negate 5.125 J/mm2 effects of ‘First Pulse’ 25% Beam P = 82 W Scanned on Overlap Qs = 30 kHz same v = powder 300 mm/s layer as An = previous 3.644 J/mm2 profile scan. 3 Circular P = 82 W 100 μm −450 μm Powder profile. Qs = 40 kHz laid as 5 concentric V = usual circles, 160 mm/s 0.1 mm offset An = to negate 5.125 J/mm2 effects of ‘First Pulse’ 0% Beam P = 82 W Scanned on Overlap Qs = 30 kHz same v = powder 300 mm/s layer as An = previous 2.733 J/mm2 profile scan. 4 Waffle 0 and P = 82 W 75 μm −525 μm Powder 90° Qs = 0 Hz laid as 700 μm (cw) usual linespacing v = (−600% Beam 240 mm/s overlap) An = 0.488 J/mm2 5 Waffle 0 and P = 82 W 75 μm −600 μm Powder 90° Qs = 0 Hz laid as 700 μm (cw) usual linespacing v = (−600% Beam 240 mm/s overlap) An = 0.488 J/mm2 6 Waffle 0 and P = 82 W 75 μm −675 μm Powder 90° Qs = 0 Hz laid as 700 μm (cw) usual linespacing v = (600% Beam 240 mm/s overlap) An = 0.488 J/mm2 7 Waffle 45 P = 82 W 75 μm −750 μm Powder and 135° Qs = 0 Hz laid as 700 μm (cw) usual linespacing v = (−600% Beam 240 mm/s overlap) An = 0.488 J/mm2 8 Waffle 45 P = 82 W 75 μm −825 μm Powder and 135° Qs = 0 Hz laid as 700 μm (cw) usual linespacing v = (−600% Beam 240 mm/s overlap) An = 0.488 J/mm2 9 Waffle 45 P = 82 W 75 μm −900 μm Powder and 135° Qs = 0 Hz laid as 700 μm (cw) usual linespacing v = (−600% Beam 240 mm/s overlap) An = 0.488 J/mm2 - The second and preferred approach uses a continuous scanning strategy whereby the pores are developed by the planar deposition of laser melted powder tracks superimposed over each other. This superimposition combined with the melt flow produces random and pseudorandom porous structures. The properties of the final structure, randomness, interconnectivity, mechanical strength and thermal response are controlled by the process parameters employed. One set of scanning parameters used was: Scanning sequences of 0° 0°0°, 90° 90° 90°, 45° 45° 45°, 135°, 135°, 135°, of layer thickness 0.1 mm were developed to form a waffle. Three layers of each were necessary to obtain sufficient web thickness in the “z” direction. The array of sequences was repeated many times to give a construct of the desired height. Laser power was 82 watts, operating frequency between 0 (cw) and 40 KHz, scan speed of between 160 and 240 mm/sec with a beam overlap of −700%.
FIG. 32 shows such a construct. - The use of an optical inspection method to determine this approximate porosity is appropriate given the sample size. This method, although not accurate due to the filter selection process, can, if used carefully, provide an indication of porosity. An average porosity level of around 25% was predicted. This porosity level falls within the range of the desired porosity for bone in-growth structures.
- In consideration of the potential application, it is important to minimize loose surface contamination and demonstrate the ability to fully clean the surface. Laser cleaning or acid etching technique may be effective. Additionally, a rigorous cleaning protocol to remove all loose powder may entail blowing the porous structure with clean dry compressed gas, followed by a period of ultrasonic agitation in a treatment fluid. Once dried, a laser scan may be used to seal any remaining loose particles.
- On examination, all candidate materials and substrates were selectively fused to produce a complex interconnected pore structure. There were small differences in certain process parameters such as speed and beam overlap percentage. From
FIG. 12 it can also be seen how the Ti build has successfully fused with the Ti alloy substrate using a laser power of 82 W cw, beam overlap of −40% and a laser scanning speed of 180 mms−1. With the ability to produce structures with a controlled porosity, this demonstrates how the Direct Laser Remelting process can be used as a surface modification technology. Certain metal combinations interacted unfavourably and resulted in formation of intermetallics, which are inherently brittle structures. To overcome this problem it may be necessary to use a bond coat with the substrate. It is then possible to build directly on to the substrate with a porous build. A typical example of the use of a bond coat is provided by the combination of titanium on to a cobalt chromium substrate. Tantalum also was an effective bond coat in this example. Note that the bond coat may be applied by laser technology, but other methods are also possible such as gas plasma deposition. - The non-contact surface profilimeotry (OSP) images shown in
FIGS. 13( a) to 13(d) show the surface profile. In addition, the Surface Data shown inFIGS. 14( a) and 14(b) and 15(a) and 15(b) show a coded profile of the plan views of the samples.FIG. 14( a) shows Ti on Ti (OSP Surface Data) where v=200 mms−1,FIG. 14( b) shows CoCr on Ti (OSP Surface Data) where v=200 mms−1, andFIG. 15( a) shows Nb on Ti (OSP Surface Data) where v=200 mms−1 andFIG. 15( b) shows Ta on Ti (OSP Surface Data) where v=200 mms−1. -
FIGS. 16 to 25 are scanning electron microscope (SEM) micrographs of a series of single layer Ti on CoCr and Ti on Ti images that were produced prior to the multi-layer builds shown inFIGS. 8 and 9 respectively and as follows. -
FIG. 16( a) shows Ti on CoCr (Single Layer; SEM Micrograph) v=160 mms−1; -
FIG. 16( b) shows Ti on CoCr (Single Layer; SEM Micrograph) v=160 mms−1; -
FIG. 17( a) shows Ti on CoCr (Single Layer; SEM Micrograph) v=170 mms−1; -
FIG. 17( b) shows Ti on CoCr (Single Layer; SEM Micrograph) v=180 mms−1; -
FIG. 18( a) shows Ti on CoCr (Single Layer; SEM Micrograph) v=190 mms−1; -
FIG. 18( b) shows Ti on CoCr (Single Layer; SEM Micrograph) v=200 mms−1; -
FIG. 19( a) shows Ti on CoCr (Single Layer; SEM Micrograph) v=210 mms−1; -
FIG. 19( b) shows Ti on CoCr (Single Layer; SEM Micrograph) v=220 mms−1; -
FIG. 20( a) shows Ti on CoCr (Single Layer; SEM Micrograph) v=230 mms−1; -
FIG. 20( b) shows Ti on CoCr (Single Layer; SEM Micrograph) v=240 mms−1; -
FIG. 21( a) shows Ti on Ti (Single Layer; SEM Micrograph) v=160 mms−1; -
FIG. 21( b) shows Ti on Ti (Single Layer; SEM Micrograph) v=170 mms−1; -
FIG. 22( a) shows Ti on Ti (Single Layer; SEM Micrograph) v=190 mms−1; -
FIG. 22( b) shows Ti on Ti (Single Layer; SEM Micrograph) v=200 mms−1; -
FIG. 23( a) shows Ti on Ti (Single Layer; SEM Micrograph) v=220 mms−1; -
FIG. 23( b) shows Ti on Ti (Single Layer; SEM Micrograph) v=230 mms−1; -
FIG. 24( a) shows Ti on Ti (Single Layer; SEM Micrograph) v=240 mms−1; -
FIG. 24( b) shows Ti on Ti (Single Layer; SEM Micrograph) v=240 mms−1; - The method according to the present invention can produce surface structures on all powder/baseplate combinations with careful selection of process parameters.
- As described above, the process is carried out on flat baseplates that provide for easy powder delivery in successive layers of around 100 μm thickness. Control of powder layer thickness is very important if consistent surface properties are required. The application of this technology can also be applied to curved surfaces such as those found in modern prosthetic devices; with refinements being made to the powder layer technique.
- The structures have all received ultrasonic and aqueous cleaning. On close examination, the resultant porous surfaces produced by the Direct Laser Remelting process exhibit small particulates that are scattered throughout the structure. It is unclear at this stage whether these particulates are bonded to the surface or loosely attached but there are means to remove the particulates if required.
- The Direct Laser Remelting process has the ability to produce porous structures that are suitable for bone in-growth applications. The powdered surfaces have undergone considerable thermal cycling culminating in rapid cooling rates that have produced very fine dendritic structures (e.g.
FIGS. 13( a) to 13(d)). - The Direct Laser Remelting process can produce effective bone in-growth surfaces and the manufacturing costs are reasonable.
- In the preceding examples, the object has been to provide a porous structure on a base but the present invention can also be used to provide a non-porous structure on such a base to form a three-dimensional structure. The same techniques can be utilized for the materials concerned but the laser processing parameters can be appropriately selected so that a substantially solid non-porous structure is achieved.
- Again, a technique can be used to deposit the powder onto a suitable carrier, for example a mold, and to carry out the process without the use of a base so that a three-dimensional structure is achieved which can be either porous, as described above, or non-porous if required.
- It will be appreciated that this method can, therefore, be used to produce article from the metals referred to which can be created to a desired shape and which may or may not require subsequent machining. Yet again, such an article can be produced so that it has a graded porosity of, e.g., non-porous through various degrees of porosity to the outer surface layer. Such articles could be surgical prostheses, parts or any other article to which this method of production would be advantageous.
Claims (22)
Priority Applications (7)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US12/386,679 US8268099B2 (en) | 2002-11-08 | 2009-04-22 | Laser-produced porous surface |
US12/843,376 US8268100B2 (en) | 2002-11-08 | 2010-07-26 | Laser-produced porous surface |
US13/605,354 US8992703B2 (en) | 2002-11-08 | 2012-09-06 | Laser-produced porous surface |
US14/671,545 US10525688B2 (en) | 2002-11-08 | 2015-03-27 | Laser-produced porous surface |
US16/690,307 US11155073B2 (en) | 2002-11-08 | 2019-11-21 | Laser-produced porous surface |
US17/176,842 US11186077B2 (en) | 2002-11-08 | 2021-02-16 | Laser-produced porous surface |
US17/401,977 US11510783B2 (en) | 2002-11-08 | 2021-08-13 | Laser-produced porous surface |
Applications Claiming Priority (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US42492302P | 2002-11-08 | 2002-11-08 | |
US42565702P | 2002-11-12 | 2002-11-12 | |
US10/704,270 US7537664B2 (en) | 2002-11-08 | 2003-11-07 | Laser-produced porous surface |
US12/386,679 US8268099B2 (en) | 2002-11-08 | 2009-04-22 | Laser-produced porous surface |
Related Parent Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/704,270 Continuation US7537664B2 (en) | 2002-11-08 | 2003-11-07 | Laser-produced porous surface |
US13/605,354 Continuation US8992703B2 (en) | 2002-11-08 | 2012-09-06 | Laser-produced porous surface |
Related Child Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US12/843,376 Continuation US8268100B2 (en) | 2002-11-08 | 2010-07-26 | Laser-produced porous surface |
Publications (2)
Publication Number | Publication Date |
---|---|
US20090286008A1 true US20090286008A1 (en) | 2009-11-19 |
US8268099B2 US8268099B2 (en) | 2012-09-18 |
Family
ID=32110369
Family Applications (8)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/704,270 Active 2024-12-03 US7537664B2 (en) | 2002-11-08 | 2003-11-07 | Laser-produced porous surface |
US12/386,679 Expired - Lifetime US8268099B2 (en) | 2002-11-08 | 2009-04-22 | Laser-produced porous surface |
US12/843,376 Expired - Lifetime US8268100B2 (en) | 2002-11-08 | 2010-07-26 | Laser-produced porous surface |
US13/605,354 Expired - Lifetime US8992703B2 (en) | 2002-11-08 | 2012-09-06 | Laser-produced porous surface |
US14/671,545 Active 2026-02-03 US10525688B2 (en) | 2002-11-08 | 2015-03-27 | Laser-produced porous surface |
US16/690,307 Expired - Lifetime US11155073B2 (en) | 2002-11-08 | 2019-11-21 | Laser-produced porous surface |
US17/176,842 Expired - Lifetime US11186077B2 (en) | 2002-11-08 | 2021-02-16 | Laser-produced porous surface |
US17/401,977 Expired - Lifetime US11510783B2 (en) | 2002-11-08 | 2021-08-13 | Laser-produced porous surface |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/704,270 Active 2024-12-03 US7537664B2 (en) | 2002-11-08 | 2003-11-07 | Laser-produced porous surface |
Family Applications After (6)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US12/843,376 Expired - Lifetime US8268100B2 (en) | 2002-11-08 | 2010-07-26 | Laser-produced porous surface |
US13/605,354 Expired - Lifetime US8992703B2 (en) | 2002-11-08 | 2012-09-06 | Laser-produced porous surface |
US14/671,545 Active 2026-02-03 US10525688B2 (en) | 2002-11-08 | 2015-03-27 | Laser-produced porous surface |
US16/690,307 Expired - Lifetime US11155073B2 (en) | 2002-11-08 | 2019-11-21 | Laser-produced porous surface |
US17/176,842 Expired - Lifetime US11186077B2 (en) | 2002-11-08 | 2021-02-16 | Laser-produced porous surface |
US17/401,977 Expired - Lifetime US11510783B2 (en) | 2002-11-08 | 2021-08-13 | Laser-produced porous surface |
Country Status (6)
Country | Link |
---|---|
US (8) | US7537664B2 (en) |
EP (1) | EP1418013B1 (en) |
AT (1) | ATE287307T1 (en) |
AU (1) | AU2003261497B2 (en) |
CA (1) | CA2448592C (en) |
DE (1) | DE60300277T2 (en) |
Cited By (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20110143094A1 (en) * | 2009-12-11 | 2011-06-16 | Ngimat Co. | Process for Forming High Surface Area Embedded Coating with High Abrasion Resistance |
US20150321289A1 (en) * | 2014-05-12 | 2015-11-12 | Siemens Energy, Inc. | Laser deposition of metal foam |
US20170021453A1 (en) * | 2013-12-23 | 2017-01-26 | General Electric Technology Gmbh | Gamma prime precipitation strengthened nickel-base superalloy for use in powder based additive manufacturing process |
WO2021097248A1 (en) * | 2019-11-14 | 2021-05-20 | University Of Washington | Closed-loop feedback for additive manufacturing simulation |
US11167375B2 (en) | 2018-08-10 | 2021-11-09 | The Research Foundation For The State University Of New York | Additive manufacturing processes and additively manufactured products |
EP2817037B1 (en) * | 2012-02-20 | 2022-08-03 | Smith & Nephew, Inc. | Methods of making porous structures |
US11897033B2 (en) | 2018-04-19 | 2024-02-13 | Compagnie Generale Des Etablissements Michelin | Process for the additive manufacturing of a three-dimensional metal part |
Families Citing this family (343)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
FR2836282B1 (en) * | 2002-02-19 | 2004-04-02 | Commissariat Energie Atomique | ALVEOLAR STRUCTURE AND METHOD OF MANUFACTURING SUCH A STRUCTURE |
US20060147332A1 (en) | 2004-12-30 | 2006-07-06 | Howmedica Osteonics Corp. | Laser-produced porous structure |
EP1418013B1 (en) | 2002-11-08 | 2005-01-19 | Howmedica Osteonics Corp. | Laser-produced porous surface |
US7666522B2 (en) * | 2003-12-03 | 2010-02-23 | IMDS, Inc. | Laser based metal deposition (LBMD) of implant structures |
US7001672B2 (en) * | 2003-12-03 | 2006-02-21 | Medicine Lodge, Inc. | Laser based metal deposition of implant structures |
US20070106374A1 (en) * | 2004-01-22 | 2007-05-10 | Isoflux, Inc. | Radiopaque coating for biomedical devices |
US20180228621A1 (en) | 2004-08-09 | 2018-08-16 | Mark A. Reiley | Apparatus, systems, and methods for the fixation or fusion of bone |
GB0422666D0 (en) * | 2004-10-12 | 2004-11-10 | Benoist Girard Sas | Prosthetic acetabular cups |
US20060133947A1 (en) * | 2004-12-21 | 2006-06-22 | United Technologies Corporation | Laser enhancements of cold sprayed deposits |
FR2884406B1 (en) | 2005-04-14 | 2008-10-17 | Memometal Technologies Soc Par | INTRAMEDULAR OSTEOSYNTHESIS DEVICE OF TWO BONE PARTS, IN PARTICULAR HAND AND / OR FOOT |
DE102005024913A1 (en) | 2005-05-31 | 2006-12-14 | Axetis Ag | Stent for insertion into vessel, comprises specifically applied coating for avoidance of new blockage |
GB0511460D0 (en) | 2005-06-06 | 2005-07-13 | Univ Liverpool | Process |
ITMI20051717A1 (en) * | 2005-09-16 | 2007-03-17 | Leader Italia S R L | DENTAL ENDOSSEO PLANT STRUCTURE WITH DEFAULT GEOMETRY SURFACE |
DE102005045699A1 (en) * | 2005-09-20 | 2007-03-29 | Michael Haas | Die casting method employs mold with areas of different thermal conductivity, setting up different rates of heat dissipation from casting |
US20070085241A1 (en) * | 2005-10-14 | 2007-04-19 | Northrop Grumman Corporation | High density performance process |
DE102005049886A1 (en) * | 2005-10-17 | 2007-04-19 | Sirona Dental Systems Gmbh | Tooth replacement part manufacturing method involves energy beam sintering powder material at the edge area to a greater density than in inner region by varying process parameters during sintering |
DE102005050665A1 (en) * | 2005-10-20 | 2007-04-26 | Bego Medical Gmbh | Layer-wise production process with grain size influencing |
US8728387B2 (en) | 2005-12-06 | 2014-05-20 | Howmedica Osteonics Corp. | Laser-produced porous surface |
US7648524B2 (en) * | 2005-12-23 | 2010-01-19 | Howmedica Osteonics Corp. | Porous tendon anchor |
US20070179607A1 (en) * | 2006-01-31 | 2007-08-02 | Zimmer Technology, Inc. | Cartilage resurfacing implant |
GB0601982D0 (en) * | 2006-02-01 | 2006-03-15 | Rolls Royce Plc | Method and apparatus for examination of objects and structures |
US9327056B2 (en) * | 2006-02-14 | 2016-05-03 | Washington State University | Bone replacement materials |
US8603180B2 (en) | 2006-02-27 | 2013-12-10 | Biomet Manufacturing, Llc | Patient-specific acetabular alignment guides |
US8591516B2 (en) | 2006-02-27 | 2013-11-26 | Biomet Manufacturing, Llc | Patient-specific orthopedic instruments |
US20150335438A1 (en) | 2006-02-27 | 2015-11-26 | Biomet Manufacturing, Llc. | Patient-specific augments |
US8568487B2 (en) | 2006-02-27 | 2013-10-29 | Biomet Manufacturing, Llc | Patient-specific hip joint devices |
US9173661B2 (en) | 2006-02-27 | 2015-11-03 | Biomet Manufacturing, Llc | Patient specific alignment guide with cutting surface and laser indicator |
US8407067B2 (en) | 2007-04-17 | 2013-03-26 | Biomet Manufacturing Corp. | Method and apparatus for manufacturing an implant |
US8608749B2 (en) | 2006-02-27 | 2013-12-17 | Biomet Manufacturing, Llc | Patient-specific acetabular guides and associated instruments |
US9345548B2 (en) | 2006-02-27 | 2016-05-24 | Biomet Manufacturing, Llc | Patient-specific pre-operative planning |
US8535387B2 (en) | 2006-02-27 | 2013-09-17 | Biomet Manufacturing, Llc | Patient-specific tools and implants |
US8092465B2 (en) | 2006-06-09 | 2012-01-10 | Biomet Manufacturing Corp. | Patient specific knee alignment guide and associated method |
US9339278B2 (en) | 2006-02-27 | 2016-05-17 | Biomet Manufacturing, Llc | Patient-specific acetabular guides and associated instruments |
US8608748B2 (en) | 2006-02-27 | 2013-12-17 | Biomet Manufacturing, Llc | Patient specific guides |
US9918740B2 (en) | 2006-02-27 | 2018-03-20 | Biomet Manufacturing, Llc | Backup surgical instrument system and method |
US9113971B2 (en) | 2006-02-27 | 2015-08-25 | Biomet Manufacturing, Llc | Femoral acetabular impingement guide |
US8377066B2 (en) | 2006-02-27 | 2013-02-19 | Biomet Manufacturing Corp. | Patient-specific elbow guides and associated methods |
US9907659B2 (en) | 2007-04-17 | 2018-03-06 | Biomet Manufacturing, Llc | Method and apparatus for manufacturing an implant |
US9289253B2 (en) | 2006-02-27 | 2016-03-22 | Biomet Manufacturing, Llc | Patient-specific shoulder guide |
US7967868B2 (en) | 2007-04-17 | 2011-06-28 | Biomet Manufacturing Corp. | Patient-modified implant and associated method |
US10278711B2 (en) | 2006-02-27 | 2019-05-07 | Biomet Manufacturing, Llc | Patient-specific femoral guide |
US7951412B2 (en) * | 2006-06-07 | 2011-05-31 | Medicinelodge Inc. | Laser based metal deposition (LBMD) of antimicrobials to implant surfaces |
US9795399B2 (en) | 2006-06-09 | 2017-10-24 | Biomet Manufacturing, Llc | Patient-specific knee alignment guide and associated method |
US8147861B2 (en) * | 2006-08-15 | 2012-04-03 | Howmedica Osteonics Corp. | Antimicrobial implant |
GB2442441B (en) * | 2006-10-03 | 2011-11-09 | Biomet Uk Ltd | Surgical instrument |
US7866372B2 (en) * | 2006-12-20 | 2011-01-11 | The Boeing Company | Method of making a heat exchanger core component |
US7810552B2 (en) * | 2006-12-20 | 2010-10-12 | The Boeing Company | Method of making a heat exchanger |
US7866377B2 (en) * | 2006-12-20 | 2011-01-11 | The Boeing Company | Method of using minimal surfaces and minimal skeletons to make heat exchanger components |
ITUD20070092A1 (en) * | 2007-05-29 | 2008-11-30 | Lima Lto S P A | PROSTHETIC ELEMENT AND RELATIVE PROCEDURE FOR IMPLEMENTATION |
EP2022447A1 (en) * | 2007-07-09 | 2009-02-11 | Astra Tech AB | Nanosurface |
US10758283B2 (en) | 2016-08-11 | 2020-09-01 | Mighty Oak Medical, Inc. | Fixation devices having fenestrations and methods for using the same |
WO2009014718A1 (en) | 2007-07-24 | 2009-01-29 | Porex Corporation | Porous laser sintered articles |
EP2231352B1 (en) | 2008-01-03 | 2013-10-16 | Arcam Ab | Method and apparatus for producing three-dimensional objects |
GB0809721D0 (en) * | 2008-05-28 | 2008-07-02 | Univ Bath | Improvements in or relating to joints and/or implants |
US20100042218A1 (en) * | 2008-08-13 | 2010-02-18 | Nebosky Paul S | Orthopaedic implant with porous structural member |
JP5774989B2 (en) | 2008-08-13 | 2015-09-09 | スメド−ティーエイ/ティーディー・エルエルシー | Orthopedic screw |
US9616205B2 (en) | 2008-08-13 | 2017-04-11 | Smed-Ta/Td, Llc | Drug delivery implants |
US20100042213A1 (en) | 2008-08-13 | 2010-02-18 | Nebosky Paul S | Drug delivery implants |
US9700431B2 (en) | 2008-08-13 | 2017-07-11 | Smed-Ta/Td, Llc | Orthopaedic implant with porous structural member |
US10842645B2 (en) | 2008-08-13 | 2020-11-24 | Smed-Ta/Td, Llc | Orthopaedic implant with porous structural member |
JP5687622B2 (en) | 2008-08-29 | 2015-03-18 | スメド−ティーエイ/ティーディー・エルエルシー | Orthopedic implant |
FR2935601B1 (en) | 2008-09-09 | 2010-10-01 | Memometal Technologies | INTRAMEDULLARY IMPLANT RESORBABLE BETWEEN TWO BONE OR TWO BONE FRAGMENTS |
DE102009014184A1 (en) * | 2008-11-07 | 2010-05-20 | Advanced Medical Technologies Ag | Implant for fusion of spinal segments |
US8821555B2 (en) | 2009-02-11 | 2014-09-02 | Howmedica Osteonics Corp. | Intervertebral implant with integrated fixation |
CA2753201C (en) | 2009-02-24 | 2019-03-19 | Mako Surgical Corp. | Prosthetic device, method of planning bone removal for implantation of prosthetic device, and robotic system |
US9220547B2 (en) | 2009-03-27 | 2015-12-29 | Spinal Elements, Inc. | Flanged interbody fusion device |
EP2424707B2 (en) | 2009-04-28 | 2021-09-29 | BAE Systems PLC | Additive layer fabrication method |
ES2663554T5 (en) | 2009-04-28 | 2022-05-06 | Bae Systems Plc | Layered additive manufacturing method |
EP2253291B1 (en) | 2009-05-19 | 2016-03-16 | National University of Ireland, Galway | A bone implant with a surface anchoring structure |
US20180253774A1 (en) * | 2009-05-19 | 2018-09-06 | Cobra Golf Incorporated | Method and system for making golf club components |
GB0910447D0 (en) | 2009-06-17 | 2009-07-29 | Ulive Entpr Ltd | Dental implant |
US9399321B2 (en) | 2009-07-15 | 2016-07-26 | Arcam Ab | Method and apparatus for producing three-dimensional objects |
DE102009028503B4 (en) | 2009-08-13 | 2013-11-14 | Biomet Manufacturing Corp. | Resection template for the resection of bones, method for producing such a resection template and operation set for performing knee joint surgery |
WO2011022560A1 (en) | 2009-08-19 | 2011-02-24 | Smith & Nephew, Inc. | Porous implant structures |
DE102009043597A1 (en) * | 2009-09-25 | 2011-04-07 | Siemens Aktiengesellschaft | Method for producing a marked object |
KR20120095377A (en) * | 2009-10-07 | 2012-08-28 | 바이오2 테크놀로지스, 아이엔씨. | Devices and methods for tissue engineering |
FR2951971B1 (en) * | 2009-11-03 | 2011-12-09 | Michelin Soc Tech | SUPPORT PLATE FOR LASER SINTERING DEVICE AND IMPROVED SINKING METHOD |
RU2627454C2 (en) * | 2009-11-12 | 2017-08-08 | Смит Энд Нефью, Инк. | Porous structures with controllable randomization and methods for their production |
JP4802277B2 (en) * | 2009-12-28 | 2011-10-26 | ナカシマメディカル株式会社 | Shock absorbing structure and manufacturing method thereof |
FR2955025B1 (en) * | 2010-01-11 | 2012-11-30 | Kasios | POROUS TITANIUM PIECE AND METHOD OF MANUFACTURING THE SAME |
DE102010008960A1 (en) * | 2010-02-23 | 2011-08-25 | EOS GmbH Electro Optical Systems, 82152 | Method and device for producing a three-dimensional object that is particularly suitable for use in microtechnology |
US8632547B2 (en) | 2010-02-26 | 2014-01-21 | Biomet Sports Medicine, Llc | Patient-specific osteotomy devices and methods |
IT1398443B1 (en) * | 2010-02-26 | 2013-02-22 | Lima Lto S P A Ora Limacorporate Spa | INTEGRATED PROSTHETIC ELEMENT |
US8468673B2 (en) | 2010-09-10 | 2013-06-25 | Bio2 Technologies, Inc. | Method of fabricating a porous orthopedic implant |
US9271744B2 (en) | 2010-09-29 | 2016-03-01 | Biomet Manufacturing, Llc | Patient-specific guide for partial acetabular socket replacement |
US8535386B2 (en) | 2010-10-21 | 2013-09-17 | Howmedica Osteonics Corp. | Stem with pressfit porous element |
CA2818195C (en) | 2010-11-18 | 2018-12-18 | Zimmer, Inc. | Resistance welding a porous metal layer to a metal substrate |
US10427235B2 (en) * | 2010-11-18 | 2019-10-01 | Zimmer, Inc. | Resistance welding a porous metal layer to a metal substrate |
US9968376B2 (en) | 2010-11-29 | 2018-05-15 | Biomet Manufacturing, Llc | Patient-specific orthopedic instruments |
DE102010063725B4 (en) * | 2010-12-21 | 2015-10-08 | Siemens Aktiengesellschaft | Component with a filled cavity, use of this component and method for its preparation |
US9073265B2 (en) | 2011-01-28 | 2015-07-07 | Arcam Ab | Method for production of a three-dimensional body |
US9241745B2 (en) | 2011-03-07 | 2016-01-26 | Biomet Manufacturing, Llc | Patient-specific femoral version guide |
US8715289B2 (en) | 2011-04-15 | 2014-05-06 | Biomet Manufacturing, Llc | Patient-specific numerically controlled instrument |
US8668700B2 (en) | 2011-04-29 | 2014-03-11 | Biomet Manufacturing, Llc | Patient-specific convertible guides |
US8956364B2 (en) | 2011-04-29 | 2015-02-17 | Biomet Manufacturing, Llc | Patient-specific partial knee guides and other instruments |
US8532807B2 (en) | 2011-06-06 | 2013-09-10 | Biomet Manufacturing, Llc | Pre-operative planning and manufacturing method for orthopedic procedure |
US9084618B2 (en) | 2011-06-13 | 2015-07-21 | Biomet Manufacturing, Llc | Drill guides for confirming alignment of patient-specific alignment guides |
CA2839706C (en) | 2011-06-23 | 2017-05-02 | Stryker Corporation | Prosthetic implant and method of implantation |
US8764760B2 (en) | 2011-07-01 | 2014-07-01 | Biomet Manufacturing, Llc | Patient-specific bone-cutting guidance instruments and methods |
US20130001121A1 (en) | 2011-07-01 | 2013-01-03 | Biomet Manufacturing Corp. | Backup kit for a patient-specific arthroplasty kit assembly |
US8597365B2 (en) | 2011-08-04 | 2013-12-03 | Biomet Manufacturing, Llc | Patient-specific pelvic implants for acetabular reconstruction |
US9295497B2 (en) | 2011-08-31 | 2016-03-29 | Biomet Manufacturing, Llc | Patient-specific sacroiliac and pedicle guides |
US9066734B2 (en) | 2011-08-31 | 2015-06-30 | Biomet Manufacturing, Llc | Patient-specific sacroiliac guides and associated methods |
US9386993B2 (en) | 2011-09-29 | 2016-07-12 | Biomet Manufacturing, Llc | Patient-specific femoroacetabular impingement instruments and methods |
US9451973B2 (en) | 2011-10-27 | 2016-09-27 | Biomet Manufacturing, Llc | Patient specific glenoid guide |
KR20130046336A (en) | 2011-10-27 | 2013-05-07 | 삼성전자주식회사 | Multi-view device of display apparatus and contol method thereof, and display system |
US9301812B2 (en) | 2011-10-27 | 2016-04-05 | Biomet Manufacturing, Llc | Methods for patient-specific shoulder arthroplasty |
EP3384858A1 (en) | 2011-10-27 | 2018-10-10 | Biomet Manufacturing, LLC | Patient-specific glenoid guides |
US9554910B2 (en) | 2011-10-27 | 2017-01-31 | Biomet Manufacturing, Llc | Patient-specific glenoid guide and implants |
US9011444B2 (en) | 2011-12-09 | 2015-04-21 | Howmedica Osteonics Corp. | Surgical reaming instrument for shaping a bone cavity |
EP2793756B1 (en) | 2011-12-23 | 2019-05-08 | The Royal Institution for the Advancement of Learning / McGill University | Bone replacement implants with mechanically biocompatible cellular material |
WO2013098135A1 (en) * | 2011-12-28 | 2013-07-04 | Arcam Ab | Method and apparatus for manufacturing porous three-dimensional articles |
EP2797730B2 (en) | 2011-12-28 | 2020-03-04 | Arcam Ab | Method and apparatus for detecting defects in freeform fabrication |
US9079248B2 (en) | 2011-12-28 | 2015-07-14 | Arcam Ab | Method and apparatus for increasing the resolution in additively manufactured three-dimensional articles |
AU2012362279A1 (en) | 2011-12-30 | 2014-07-24 | Howmedica Osteonics Corp. | Systems for preparing bone voids to receive a prosthesis |
US11304811B2 (en) | 2012-01-17 | 2022-04-19 | KYOCERA Medical Technologies, Inc. | Surgical implant devices incorporating porous surfaces and associated method of manufacture |
US10765530B2 (en) | 2012-06-21 | 2020-09-08 | Renovis Surgical Technologies, Inc. | Surgical implant devices incorporating porous surfaces |
CN104168854B (en) * | 2012-01-24 | 2017-02-22 | 史密夫和内修有限公司 | Porous structure and methods of making same |
US9237950B2 (en) | 2012-02-02 | 2016-01-19 | Biomet Manufacturing, Llc | Implant with patient-specific porous structure |
US9364896B2 (en) | 2012-02-07 | 2016-06-14 | Medical Modeling Inc. | Fabrication of hybrid solid-porous medical implantable devices with electron beam melting technology |
US10363140B2 (en) | 2012-03-09 | 2019-07-30 | Si-Bone Inc. | Systems, device, and methods for joint fusion |
WO2013134670A1 (en) | 2012-03-09 | 2013-09-12 | Si-Bone Inc. | Integrated implant |
US9180010B2 (en) | 2012-04-06 | 2015-11-10 | Howmedica Osteonics Corp. | Surface modified unit cell lattice structures for optimized secure freeform fabrication |
US9135374B2 (en) | 2012-04-06 | 2015-09-15 | Howmedica Osteonics Corp. | Surface modified unit cell lattice structures for optimized secure freeform fabrication |
ES2828357T3 (en) | 2012-05-04 | 2021-05-26 | Si Bone Inc | Fenestrated implant |
US9126167B2 (en) | 2012-05-11 | 2015-09-08 | Arcam Ab | Powder distribution in additive manufacturing |
US10154913B2 (en) | 2012-06-21 | 2018-12-18 | Renovis Surgical Technologies, Inc. | Surgical implant devices incorporating porous surfaces and a locking plate |
US8900303B2 (en) | 2012-07-09 | 2014-12-02 | Howmedica Osteonics Corp. | Porous bone reinforcements |
US8843229B2 (en) * | 2012-07-20 | 2014-09-23 | Biomet Manufacturing, Llc | Metallic structures having porous regions from imaged bone at pre-defined anatomic locations |
US9415137B2 (en) * | 2012-08-22 | 2016-08-16 | Biomet Manufacturing, Llc. | Directional porous coating |
US20140067080A1 (en) * | 2012-09-05 | 2014-03-06 | Christopher G. Sidebotham | Hip stem prosthesis with a porous collar to allow for bone ingrowth |
US20140076749A1 (en) * | 2012-09-14 | 2014-03-20 | Raytheon Company | Variable density desiccator housing and method of manufacturing |
EP2916980B1 (en) | 2012-11-06 | 2016-06-01 | Arcam Ab | Powder pre-processing for additive manufacturing |
US9060788B2 (en) | 2012-12-11 | 2015-06-23 | Biomet Manufacturing, Llc | Patient-specific acetabular guide for anterior approach |
US9907654B2 (en) * | 2012-12-11 | 2018-03-06 | Dr. H.C. Robert Mathys Stiftung | Bone substitute and method for producing the same |
US9204977B2 (en) | 2012-12-11 | 2015-12-08 | Biomet Manufacturing, Llc | Patient-specific acetabular guide for anterior approach |
DE112013006029T5 (en) | 2012-12-17 | 2015-09-17 | Arcam Ab | Method and device for additive manufacturing |
WO2014095200A1 (en) | 2012-12-17 | 2014-06-26 | Arcam Ab | Additive manufacturing method and apparatus |
US9763791B2 (en) | 2013-02-06 | 2017-09-19 | Howmedica Osteonics Corp. | Femoral prosthesis head |
EP2964802A4 (en) * | 2013-03-05 | 2016-11-02 | Pcc Structurals Inc | BONDING OF TITANIUM COATING TO CAST CoCr |
US9949837B2 (en) | 2013-03-07 | 2018-04-24 | Howmedica Osteonics Corp. | Partially porous bone implant keel |
WO2014137876A2 (en) | 2013-03-08 | 2014-09-12 | Stryker Corporation | Bone pads |
US9839438B2 (en) | 2013-03-11 | 2017-12-12 | Biomet Manufacturing, Llc | Patient-specific glenoid guide with a reusable guide holder |
US9579107B2 (en) | 2013-03-12 | 2017-02-28 | Biomet Manufacturing, Llc | Multi-point fit for patient specific guide |
US9498233B2 (en) | 2013-03-13 | 2016-11-22 | Biomet Manufacturing, Llc. | Universal acetabular guide and associated hardware |
US9826981B2 (en) | 2013-03-13 | 2017-11-28 | Biomet Manufacturing, Llc | Tangential fit of patient-specific guides |
US9526513B2 (en) | 2013-03-13 | 2016-12-27 | Howmedica Osteonics Corp. | Void filling joint prosthesis and associated instruments |
US9517145B2 (en) | 2013-03-15 | 2016-12-13 | Biomet Manufacturing, Llc | Guide alignment system and method |
JP2016513551A (en) | 2013-03-15 | 2016-05-16 | マコ サージカル コーポレーション | Unicondylar tibial knee implant |
US9408699B2 (en) | 2013-03-15 | 2016-08-09 | Smed-Ta/Td, Llc | Removable augment for medical implant |
US9681966B2 (en) | 2013-03-15 | 2017-06-20 | Smed-Ta/Td, Llc | Method of manufacturing a tubular medical implant |
US9724203B2 (en) | 2013-03-15 | 2017-08-08 | Smed-Ta/Td, Llc | Porous tissue ingrowth structure |
US9550207B2 (en) | 2013-04-18 | 2017-01-24 | Arcam Ab | Method and apparatus for additive manufacturing |
US9676031B2 (en) | 2013-04-23 | 2017-06-13 | Arcam Ab | Method and apparatus for forming a three-dimensional article |
US9415443B2 (en) | 2013-05-23 | 2016-08-16 | Arcam Ab | Method and apparatus for additive manufacturing |
US9468973B2 (en) | 2013-06-28 | 2016-10-18 | Arcam Ab | Method and apparatus for additive manufacturing |
CN105578994B (en) * | 2013-07-24 | 2019-08-02 | 雷诺维斯外科技术公司 | Combine the surgical implant device of porous surface |
US10016811B2 (en) * | 2013-08-09 | 2018-07-10 | David J. Neal | Orthopedic implants and methods of manufacturing orthopedic implants |
WO2015073081A1 (en) * | 2013-08-20 | 2015-05-21 | The Trustees Of Princeton University | Density enhancement methods and compositions |
US9505057B2 (en) | 2013-09-06 | 2016-11-29 | Arcam Ab | Powder distribution in additive manufacturing of three-dimensional articles |
US9676032B2 (en) | 2013-09-20 | 2017-06-13 | Arcam Ab | Method for additive manufacturing |
EP3052037B1 (en) * | 2013-10-02 | 2022-08-24 | Kyocera Medical Technologies, Inc. | Surgical implant devices incorporating porous surfaces and a locking plate |
US20150112349A1 (en) | 2013-10-21 | 2015-04-23 | Biomet Manufacturing, Llc | Ligament Guide Registration |
US10434572B2 (en) | 2013-12-19 | 2019-10-08 | Arcam Ab | Method for additive manufacturing |
US9802253B2 (en) | 2013-12-16 | 2017-10-31 | Arcam Ab | Additive manufacturing of three-dimensional articles |
US10130993B2 (en) | 2013-12-18 | 2018-11-20 | Arcam Ab | Additive manufacturing of three-dimensional articles |
US9789563B2 (en) | 2013-12-20 | 2017-10-17 | Arcam Ab | Method for additive manufacturing |
EP3092096A4 (en) * | 2014-01-09 | 2017-03-08 | United Technologies Corporation | Material and processes for additively manufacturing one or more parts |
US9789541B2 (en) | 2014-03-07 | 2017-10-17 | Arcam Ab | Method for additive manufacturing of three-dimensional articles |
US20150283613A1 (en) | 2014-04-02 | 2015-10-08 | Arcam Ab | Method for fusing a workpiece |
US10282488B2 (en) | 2014-04-25 | 2019-05-07 | Biomet Manufacturing, Llc | HTO guide with optional guided ACL/PCL tunnels |
US10842634B2 (en) | 2014-05-02 | 2020-11-24 | The Royal Institution For The Advancement Of Learning/Mcgill University | Structural porous biomaterial and implant formed of same |
US9408616B2 (en) | 2014-05-12 | 2016-08-09 | Biomet Manufacturing, Llc | Humeral cut guide |
US10111753B2 (en) | 2014-05-23 | 2018-10-30 | Titan Spine, Inc. | Additive and subtractive manufacturing process for producing implants with homogeneous body substantially free of pores and inclusions |
US9839436B2 (en) | 2014-06-03 | 2017-12-12 | Biomet Manufacturing, Llc | Patient-specific glenoid depth control |
US9561040B2 (en) | 2014-06-03 | 2017-02-07 | Biomet Manufacturing, Llc | Patient-specific glenoid depth control |
GB2541833B (en) * | 2014-06-05 | 2021-03-17 | Ossis Ltd | Improvements to implant surfaces |
US10687956B2 (en) | 2014-06-17 | 2020-06-23 | Titan Spine, Inc. | Corpectomy implants with roughened bioactive lateral surfaces |
BE1022586B1 (en) * | 2014-06-18 | 2016-06-10 | Cenat Bvba | DEVICE AND METHOD FOR ADDITIVE PRODUCTION |
US10327916B2 (en) | 2014-07-03 | 2019-06-25 | Howmedica Osteonics Corp. | Impact absorbing pad |
RU2571245C1 (en) * | 2014-07-22 | 2015-12-20 | Федеральное государственное бюджетное образовательное учреждение высшего профессионального образования "Сибирский государственный индустриальный университет" | Surface hardening of 20x13 steel |
US10561456B2 (en) | 2014-07-24 | 2020-02-18 | KYOCERA Medical Technologies, Inc. | Bone screw incorporating a porous surface formed by an additive manufacturing process |
CN104207867B (en) * | 2014-08-13 | 2017-02-22 | 中国科学院福建物质结构研究所 | Low-modulus medical implant porous scaffold structure |
US9341467B2 (en) | 2014-08-20 | 2016-05-17 | Arcam Ab | Energy beam position verification |
US10166033B2 (en) | 2014-09-18 | 2019-01-01 | Si-Bone Inc. | Implants for bone fixation or fusion |
US9833245B2 (en) | 2014-09-29 | 2017-12-05 | Biomet Sports Medicine, Llc | Tibial tubercule osteotomy |
US9826994B2 (en) | 2014-09-29 | 2017-11-28 | Biomet Manufacturing, Llc | Adjustable glenoid pin insertion guide |
JP6174655B2 (en) | 2014-10-21 | 2017-08-02 | ユナイテッド テクノロジーズ コーポレイションUnited Technologies Corporation | Ducted heat exchanger system for gas turbine engine and method for manufacturing heat exchanger for gas turbine engine |
CN105525992B (en) | 2014-10-21 | 2020-04-14 | 联合工艺公司 | Additive manufactured ducted heat exchanger system with additive manufactured cowling |
US20160143663A1 (en) | 2014-11-24 | 2016-05-26 | Stryker European Holdings I, Llc | Strut plate and cabling system |
US20160167303A1 (en) | 2014-12-15 | 2016-06-16 | Arcam Ab | Slicing method |
US10299929B2 (en) | 2015-01-12 | 2019-05-28 | Howmedica Osteonics Corp. | Bone void forming apparatus |
AU2016200179B2 (en) | 2015-01-14 | 2020-09-17 | Stryker European Operations Holdings Llc | Spinal implant with porous and solid surfaces |
CA2917503A1 (en) | 2015-01-14 | 2016-07-14 | Stryker European Holdings I, Llc | Spinal implant with fluid delivery capabilities |
US9721755B2 (en) | 2015-01-21 | 2017-08-01 | Arcam Ab | Method and device for characterizing an electron beam |
US10070962B1 (en) | 2015-02-13 | 2018-09-11 | Nextstep Arthropedix, LLC | Medical implants having desired surface features and methods of manufacturing |
US9820868B2 (en) | 2015-03-30 | 2017-11-21 | Biomet Manufacturing, Llc | Method and apparatus for a pin apparatus |
US11014161B2 (en) | 2015-04-21 | 2021-05-25 | Arcam Ab | Method for additive manufacturing |
US9918849B2 (en) | 2015-04-29 | 2018-03-20 | Institute for Musculoskeletal Science and Education, Ltd. | Coiled implants and systems and methods of use thereof |
US10449051B2 (en) | 2015-04-29 | 2019-10-22 | Institute for Musculoskeletal Science and Education, Ltd. | Implant with curved bone contacting elements |
CA2930123A1 (en) | 2015-05-18 | 2016-11-18 | Stryker European Holdings I, Llc | Partially resorbable implants and methods |
CN107835669A (en) | 2015-05-22 | 2018-03-23 | Ebm融合解决方案有限责任公司 | Joint or section bone implant for malformation correction |
GB201509284D0 (en) * | 2015-05-29 | 2015-07-15 | M & I Materials Ltd | Selective laser melting |
US10568647B2 (en) | 2015-06-25 | 2020-02-25 | Biomet Manufacturing, Llc | Patient-specific humeral guide designs |
US10226262B2 (en) | 2015-06-25 | 2019-03-12 | Biomet Manufacturing, Llc | Patient-specific humeral guide designs |
US10807187B2 (en) | 2015-09-24 | 2020-10-20 | Arcam Ab | X-ray calibration standard object |
US11571748B2 (en) | 2015-10-15 | 2023-02-07 | Arcam Ab | Method and apparatus for producing a three-dimensional article |
US10525531B2 (en) | 2015-11-17 | 2020-01-07 | Arcam Ab | Additive manufacturing of three-dimensional articles |
US10610930B2 (en) | 2015-11-18 | 2020-04-07 | Arcam Ab | Additive manufacturing of three-dimensional articles |
AU2016355581B2 (en) | 2015-11-20 | 2022-09-08 | Titan Spine, Inc. | Processes for additively manufacturing orthopedic implants |
TWI726940B (en) | 2015-11-20 | 2021-05-11 | 美商泰坦脊柱股份有限公司 | Processes for additively manufacturing orthopedic implants |
US10596660B2 (en) | 2015-12-15 | 2020-03-24 | Howmedica Osteonics Corp. | Porous structures produced by additive layer manufacturing |
KR20180095853A (en) | 2015-12-16 | 2018-08-28 | 너바시브 인코퍼레이티드 | Porous Spine Fusion Implant |
WO2017117527A1 (en) * | 2015-12-30 | 2017-07-06 | Mott Corporation | Porous devices made by laser additive manufacturing |
US10831180B2 (en) * | 2016-02-25 | 2020-11-10 | General Electric Company | Multivariate statistical process control of laser powder bed additive manufacturing |
US11247274B2 (en) | 2016-03-11 | 2022-02-15 | Arcam Ab | Method and apparatus for forming a three-dimensional article |
AU2017202311B2 (en) | 2016-04-07 | 2022-03-03 | Howmedica Osteonics Corp. | Expandable interbody implant |
EP3245982B1 (en) | 2016-05-20 | 2023-11-01 | Howmedica Osteonics Corp. | Expandable interbody implant with lordosis correction |
US10549348B2 (en) | 2016-05-24 | 2020-02-04 | Arcam Ab | Method for additive manufacturing |
US11325191B2 (en) | 2016-05-24 | 2022-05-10 | Arcam Ab | Method for additive manufacturing |
US10525547B2 (en) | 2016-06-01 | 2020-01-07 | Arcam Ab | Additive manufacturing of three-dimensional articles |
EP3251621B1 (en) | 2016-06-03 | 2021-01-20 | Stryker European Holdings I, LLC | Intramedullary implant |
US10765975B2 (en) * | 2016-07-01 | 2020-09-08 | Caterpillar Inc. | Filter element and method of manufacturing a filter element |
AU2017204355B2 (en) | 2016-07-08 | 2021-09-09 | Mako Surgical Corp. | Scaffold for alloprosthetic composite implant |
US10456262B2 (en) | 2016-08-02 | 2019-10-29 | Howmedica Osteonics Corp. | Patient-specific implant flanges with bone side porous ridges |
EP3493768A1 (en) | 2016-08-03 | 2019-06-12 | Titan Spine, Inc. | Implant surfaces that enhance osteoinduction |
US10743890B2 (en) | 2016-08-11 | 2020-08-18 | Mighty Oak Medical, Inc. | Drill apparatus and surgical fixation devices and methods for using the same |
US10639160B2 (en) | 2016-08-24 | 2020-05-05 | Howmedica Osteonics Corp. | Peek femoral component with segmented TI foam in-growth |
US10478312B2 (en) | 2016-10-25 | 2019-11-19 | Institute for Musculoskeletal Science and Education, Ltd. | Implant with protected fusion zones |
US10792757B2 (en) | 2016-10-25 | 2020-10-06 | Arcam Ab | Method and apparatus for additive manufacturing |
US11033394B2 (en) | 2016-10-25 | 2021-06-15 | Institute for Musculoskeletal Science and Education, Ltd. | Implant with multi-layer bone interfacing lattice |
CN106344221A (en) * | 2016-10-26 | 2017-01-25 | 四川大学 | Bonelike porous biomechanical bionic designed spinal fusion device and preparation method and use thereof |
US10987752B2 (en) | 2016-12-21 | 2021-04-27 | Arcam Ab | Additive manufacturing of three-dimensional articles |
CN106735174B (en) * | 2016-12-29 | 2019-05-28 | 东莞深圳清华大学研究院创新中心 | A kind of 3D printing metal-base composites and preparation method thereof |
EP3573553A1 (en) | 2017-01-27 | 2019-12-04 | Zimmer, Inc. | Porous fixation devices and methods |
WO2018143841A2 (en) * | 2017-02-01 | 2018-08-09 | ПОПОВ, Дмитрий Александрович | Bone tissue augmentation for cancellous bone and articular surface replacement |
US11406502B2 (en) | 2017-03-02 | 2022-08-09 | Optimotion Implants LLC | Orthopedic implants and methods |
US10905436B2 (en) | 2017-03-02 | 2021-02-02 | Optimotion Implants, Llc | Knee arthroplasty systems and methods |
US10940024B2 (en) | 2017-07-26 | 2021-03-09 | Optimotion Implants LLC | Universal femoral trial system and methods |
US10357377B2 (en) | 2017-03-13 | 2019-07-23 | Institute for Musculoskeletal Science and Education, Ltd. | Implant with bone contacting elements having helical and undulating planar geometries |
US10512549B2 (en) | 2017-03-13 | 2019-12-24 | Institute for Musculoskeletal Science and Education, Ltd. | Implant with structural members arranged around a ring |
US10722310B2 (en) | 2017-03-13 | 2020-07-28 | Zimmer Biomet CMF and Thoracic, LLC | Virtual surgery planning system and method |
US11059123B2 (en) | 2017-04-28 | 2021-07-13 | Arcam Ab | Additive manufacturing of three-dimensional articles |
AU2018203479A1 (en) | 2017-05-18 | 2018-12-06 | Howmedica Osteonics Corp. | High fatigue strength porous structure |
EP3415108A1 (en) | 2017-05-25 | 2018-12-19 | Stryker European Holdings I, LLC | Fusion cage with integrated fixation and insertion features |
US10940666B2 (en) | 2017-05-26 | 2021-03-09 | Howmedica Osteonics Corp. | Packaging structures and additive manufacturing thereof |
US11292062B2 (en) | 2017-05-30 | 2022-04-05 | Arcam Ab | Method and device for producing three-dimensional objects |
US10646345B2 (en) | 2017-06-02 | 2020-05-12 | Howmedica Osteonics Corp. | Implant with hole having porous structure for soft tissue fixation |
EP3412252B1 (en) | 2017-06-09 | 2020-02-12 | Howmedica Osteonics Corp. | Polymer interlock support structure |
US11628517B2 (en) | 2017-06-15 | 2023-04-18 | Howmedica Osteonics Corp. | Porous structures produced by additive layer manufacturing |
US11006981B2 (en) | 2017-07-07 | 2021-05-18 | K2M, Inc. | Surgical implant and methods of additive manufacturing |
CN107498045B (en) * | 2017-08-07 | 2019-05-14 | 华南理工大学 | A kind of increasing material manufacturing method of the high-strength brass alloys of leadless environment-friendly |
CN111051046B (en) * | 2017-08-31 | 2022-02-15 | 惠普发展公司,有限责任合伙企业 | Printer with a movable platen |
EP3456294A1 (en) | 2017-09-15 | 2019-03-20 | Stryker European Holdings I, LLC | Intervertebral body fusion device expanded with hardening material |
EP3459502A1 (en) | 2017-09-20 | 2019-03-27 | Stryker European Holdings I, LLC | Spinal implants |
US10828077B2 (en) | 2017-09-22 | 2020-11-10 | Howmedica Osteonics Corp. | Distal radius wedge screw |
EP3687422A4 (en) | 2017-09-26 | 2021-09-22 | SI-Bone, Inc. | Systems and methods for decorticating the sacroiliac joint |
US20190099809A1 (en) | 2017-09-29 | 2019-04-04 | Arcam Ab | Method and apparatus for additive manufacturing |
US11737880B2 (en) | 2017-10-03 | 2023-08-29 | Howmedica Osteonics Corp. | Integrated spring for soft tissue attachment |
EP3479798B1 (en) | 2017-11-03 | 2023-06-21 | Howmedica Osteonics Corp. | Flexible construct for femoral reconstruction |
US10529070B2 (en) | 2017-11-10 | 2020-01-07 | Arcam Ab | Method and apparatus for detecting electron beam source filament wear |
US10940015B2 (en) | 2017-11-21 | 2021-03-09 | Institute for Musculoskeletal Science and Education, Ltd. | Implant with improved flow characteristics |
US10744001B2 (en) | 2017-11-21 | 2020-08-18 | Institute for Musculoskeletal Science and Education, Ltd. | Implant with improved bone contact |
US11072117B2 (en) | 2017-11-27 | 2021-07-27 | Arcam Ab | Platform device |
US10821721B2 (en) | 2017-11-27 | 2020-11-03 | Arcam Ab | Method for analysing a build layer |
EP3501432A1 (en) | 2017-12-20 | 2019-06-26 | Stryker European Holdings I, LLC | Joint instrumentation |
US11517975B2 (en) | 2017-12-22 | 2022-12-06 | Arcam Ab | Enhanced electron beam generation |
WO2019140240A1 (en) | 2018-01-11 | 2019-07-18 | K2M, Inc. | Implants and instruments with flexible features |
US11284927B2 (en) | 2018-02-02 | 2022-03-29 | Stryker European Holdings I, Llc | Orthopedic screw and porous structures thereof |
US10800101B2 (en) | 2018-02-27 | 2020-10-13 | Arcam Ab | Compact build tank for an additive manufacturing apparatus |
US11267051B2 (en) | 2018-02-27 | 2022-03-08 | Arcam Ab | Build tank for an additive manufacturing apparatus |
US10932911B2 (en) | 2018-03-01 | 2021-03-02 | Biomedtrix, Llc | Implant for osteotomy and canine osteotomy method |
EP3773342A1 (en) | 2018-03-26 | 2021-02-17 | DePuy Synthes Products, Inc. | Three-dimensional porous structures for bone ingrowth and methods for producing |
US11400519B2 (en) | 2018-03-29 | 2022-08-02 | Arcam Ab | Method and device for distributing powder material |
WO2019186505A1 (en) | 2018-03-30 | 2019-10-03 | DePuy Synthes Products, Inc. | Hybrid fixation features for three-dimensional porous structures for bone ingrowth and methods for producing |
CN111936087A (en) | 2018-03-30 | 2020-11-13 | 德普伊新特斯产品公司 | Surface texture of three-dimensional porous structure for bone ingrowth and method of making |
US11744695B2 (en) | 2018-04-06 | 2023-09-05 | Howmedica Osteonics Corp. | Soft tissue attachment device |
US10744003B2 (en) | 2018-05-08 | 2020-08-18 | Globus Medical, Inc. | Intervertebral spinal implant |
US10517739B2 (en) | 2018-05-08 | 2019-12-31 | Globus Medical, Inc. | Intervertebral spinal implant |
US10682238B2 (en) | 2018-05-08 | 2020-06-16 | Globus Medical, Inc. | Intervertebral spinal implant |
AU2019203591A1 (en) | 2018-05-25 | 2019-12-12 | Howmedica Osteonics Corp. | Variable thickness femoral augments |
KR102115229B1 (en) * | 2018-06-20 | 2020-05-27 | 한국생산기술연구원 | One-step manufacturing method of laminated molding porous component which has curved surface |
KR102115225B1 (en) * | 2018-06-20 | 2020-05-27 | 한국생산기술연구원 | One-step manufacturing method of laminated molding porous component |
US11065126B2 (en) | 2018-08-09 | 2021-07-20 | Stryker European Operations Holdings Llc | Interbody implants and optimization features thereof |
US10780498B2 (en) * | 2018-08-22 | 2020-09-22 | General Electric Company | Porous tools and methods of making the same |
WO2020061487A1 (en) | 2018-09-20 | 2020-03-26 | Amendia, Inc. d/b/a Spinal Elements | Spinal implant device |
AU2019355859A1 (en) | 2018-10-01 | 2021-05-13 | K2M, Inc. | Graft scaffold |
IT201800009553A1 (en) | 2018-10-17 | 2020-04-17 | Andrea Brovelli | METHOD FOR MAKING SCREWS FOR INTRA-BONE FIXATIONS AND SCREWS OBTAINED BY THIS METHOD |
US11534961B2 (en) | 2018-11-09 | 2022-12-27 | General Electric Company | Melt pool monitoring system and method for detecting errors in a multi-laser additive manufacturing process |
US11534257B2 (en) | 2018-11-20 | 2022-12-27 | Howmedica Osteonics Corp. | Lattice impaction pad |
US11717265B2 (en) | 2018-11-30 | 2023-08-08 | General Electric Company | Methods and systems for an acoustic attenuating material |
EP3666228A1 (en) | 2018-12-14 | 2020-06-17 | Howmedica Osteonics Corp. | Augmented, just-in-time, patient-specific implant manufacture |
CN111388156B (en) * | 2018-12-29 | 2021-09-10 | 上海微创医疗器械(集团)有限公司 | Biological coatings and implants |
AU2020200077A1 (en) | 2019-01-07 | 2020-07-23 | Howmedica Osteonics Corp. | Support frame |
US11298244B2 (en) | 2019-01-31 | 2022-04-12 | K2M, Inc. | Interbody implants and instrumentation |
US11039931B2 (en) | 2019-02-01 | 2021-06-22 | Globus Medical, Inc. | Intervertebral spinal implant |
US11369419B2 (en) | 2019-02-14 | 2022-06-28 | Si-Bone Inc. | Implants for spinal fixation and or fusion |
AU2020223180A1 (en) | 2019-02-14 | 2021-07-22 | Si-Bone Inc. | Implants for spinal fixation and or fusion |
CN109811289B (en) * | 2019-02-27 | 2020-11-06 | 中国科学院宁波工业技术研究院慈溪生物医学工程研究所 | Surface modified titanium alloy and preparation method and application thereof |
US20200281736A1 (en) | 2019-03-04 | 2020-09-10 | K2M, Inc. | Intervertebral Implant Assembly and Instruments Therefor |
WO2020254145A1 (en) * | 2019-06-19 | 2020-12-24 | The Swatch Group Research And Development Ltd | Method for laser beam additive manufacturing of a machine part with technical and/or decorative function and machine part with technical and/or decorative function |
AU2020210308A1 (en) | 2019-08-01 | 2021-02-18 | Howmedica Osteonics Corp. | Multi-stage additive manufacturing process with inserts |
CN110421172A (en) * | 2019-08-27 | 2019-11-08 | 西安九洲生物材料有限公司 | A method of medical porous tantalum part is prepared based on selective laser melting process |
US11534307B2 (en) | 2019-09-16 | 2022-12-27 | K2M, Inc. | 3D printed cervical standalone implant |
EP4034044B1 (en) | 2019-09-25 | 2023-08-16 | DePuy Ireland Unlimited Company | Three-dimensional porous structures for bone ingrowth |
US11130131B2 (en) * | 2019-09-26 | 2021-09-28 | Lawrence Livermore National Security, Llc | Lattice microfluidics |
US11351034B2 (en) | 2019-09-30 | 2022-06-07 | DePuy Synthes Products, Inc. | Patient specific femoral prosthesis |
US11576787B2 (en) | 2019-09-30 | 2023-02-14 | DePuy Synthes Products, Inc. | Patient specific femoral prosthesis |
WO2021084484A2 (en) | 2019-10-29 | 2021-05-06 | Stryker European Operations Limited | Surgical navigation tracker, system, and method |
US11278416B2 (en) | 2019-11-14 | 2022-03-22 | Howmedica Osteonics Corp. | Concentric keel TKA |
EP4065015A4 (en) | 2019-11-27 | 2024-01-03 | Si Bone Inc | Bone stabilizing implants and methods of placement across si joints |
US11707361B2 (en) | 2020-02-05 | 2023-07-25 | K2M, Inc. | Flexible interbody implant |
US11806955B2 (en) | 2020-02-26 | 2023-11-07 | Depuy Ireland Unlimited Company | Method for testing additively manufactured orthopaedic prosthetic components |
AU2020437666A1 (en) | 2020-03-25 | 2022-09-22 | Encore Medical, Lp Dba Djo Surgical | Joint implants having porous structures formed utilizing additive manufacturing and related systems and methods |
AU2021202801A1 (en) | 2020-05-07 | 2021-11-25 | Howmedica Osteonics Corp. | Stemless metaphyseal humeral implant |
AU2021202888A1 (en) | 2020-05-26 | 2021-12-16 | Howmedica Osteonics Corp. | Medial trochanteric plate fixation |
AU2021203588A1 (en) | 2020-06-03 | 2021-12-23 | Howmedica Osteonics Corp. | Intercalary endoprosthesis |
US11745267B2 (en) * | 2020-06-24 | 2023-09-05 | National Cheng Kung University | Additive manufacturing method |
CN116438054A (en) | 2020-09-11 | 2023-07-14 | 哈佩脊椎有限责任公司 | Methods for forming implantable medical devices having varying compositions and porous structures |
US20230404773A1 (en) | 2020-10-02 | 2023-12-21 | K2M, Inc. | Spinal Interbody Implants |
US20230380983A1 (en) | 2020-10-14 | 2023-11-30 | K2M, Inc. | Spinal Interbody Implants |
JP2022072723A (en) * | 2020-10-30 | 2022-05-17 | セイコーエプソン株式会社 | Three-dimensional molding apparatus |
BE1028795B1 (en) * | 2020-11-12 | 2022-06-13 | Umc Utrecht Holding Bv | ACETABULAR IMPLANT AND PROCEDURE FOR DEFORMING THIS IMPLANT |
EP4000555A1 (en) * | 2020-11-13 | 2022-05-25 | Common Sense Engineering and Consult | An anatomical dental implant arranged to be implanted in a naturally occurring cavity of the jawbone |
US11911284B2 (en) | 2020-11-19 | 2024-02-27 | Spinal Elements, Inc. | Curved expandable interbody devices and deployment tools |
AU2021397743A1 (en) | 2020-12-09 | 2023-06-22 | Si-Bone Inc. | Sacro-iliac joint stabilizing implants and methods of implantation |
EP4019164A1 (en) * | 2020-12-22 | 2022-06-29 | Siemens Energy Global GmbH & Co. KG | Radiation strategy in additive production with pulsed irradiation |
FR3118429B1 (en) * | 2020-12-30 | 2023-11-24 | Commissariat Energie Atomique | Manufacturing process for a functional metal part delimiting a porous filtration media, using an additive manufacturing method, and functional part obtained |
CN112974804A (en) * | 2021-02-09 | 2021-06-18 | 广东省科学院新材料研究所 | Structure-controllable porous material additive manufacturing method |
CN112958906B (en) * | 2021-03-25 | 2022-02-18 | 南京航空航天大学 | Laser processing device and method suitable for AlN plate |
CN113290242A (en) * | 2021-04-26 | 2021-08-24 | 华中科技大学 | Micro-nano porous functional device, additive manufacturing method and application thereof |
CN113289057B (en) * | 2021-05-19 | 2022-10-14 | 北京爱康宜诚医疗器材有限公司 | Tantalum-coated orthopedic implant material, preparation method thereof and orthopedic implant |
US20220387163A1 (en) | 2021-06-08 | 2022-12-08 | Howmedica Osteonics Corp. | Additive Manufacturing of Porous Coatings Separate From Substrate |
US20220410272A1 (en) | 2021-06-29 | 2022-12-29 | Howmedica Osteonics Corp. | Supports For Cantilevered Elements During Additive Manufacturing And Methods Of Forming Such Supports |
US20230028894A1 (en) * | 2021-07-16 | 2023-01-26 | Wisconsin Alumni Research Foundation | Additive manufacturing with sealed pores |
AU2022256159A1 (en) | 2021-10-25 | 2023-05-11 | Howmedica Osteonics Corp. | Porous structure placement configured for manufacturing |
CN113953527B (en) * | 2021-10-29 | 2023-04-14 | 江苏科技大学 | Self-adaptive layering method for laser deposition/ultrasonic treatment synchronous additive manufacturing |
CN114226755B (en) * | 2021-12-21 | 2023-04-07 | 清华大学 | Metal-ceramic composite lattice manufacturing method and metal-ceramic composite lattice structure |
EP4245242A1 (en) | 2022-03-18 | 2023-09-20 | Stryker Australia PTY LTD | Bone resection scoring and planning |
CN114632948B (en) * | 2022-03-21 | 2022-11-15 | 中国海洋大学 | Plasma and laser composite additive manufacturing method |
CN114888304B (en) * | 2022-05-11 | 2023-06-20 | 华东理工大学 | Manufacturing method of composite porous structure liquid absorption core |
AU2023202887A1 (en) | 2022-05-12 | 2023-11-30 | Howmedica Osteonics Corp. | Fatigue resistant porous structure |
CN115533122A (en) * | 2022-12-01 | 2022-12-30 | 四川工程职业技术学院 | Iron-based alloy body and forming method and application thereof |
Citations (96)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US14403A (en) * | 1856-03-11 | Improved spirit blow-pipe | ||
US3605123A (en) * | 1969-04-29 | 1971-09-20 | Melpar Inc | Bone implant |
US3806961A (en) * | 1972-02-16 | 1974-04-30 | Sulzer Ag | Phosthetic patella implant |
US3816855A (en) * | 1971-06-01 | 1974-06-18 | Nat Res Dev | Knee joint prosthesis |
US4085466A (en) * | 1974-11-18 | 1978-04-25 | National Research Development Corporation | Prosthetic joint device |
US4164794A (en) * | 1977-04-14 | 1979-08-21 | Union Carbide Corporation | Prosthetic devices having coatings of selected porous bioengineering thermoplastics |
US4202055A (en) * | 1976-05-12 | 1980-05-13 | Battelle-Institut E.V. | Anchorage for highly stressed endoprostheses |
US4218494A (en) * | 1978-07-04 | 1980-08-19 | Centro Richerche Fiat S.P.A. | Process for coating a metallic surface with a wear-resistant material |
US4305340A (en) * | 1978-02-24 | 1981-12-15 | Yuwa Sangyo Kabushiki Kaisha | Method of forming a box-shaped structure from a foldable metal sheet |
US4344193A (en) * | 1980-11-28 | 1982-08-17 | Kenny Charles H | Meniscus prosthesis |
US4385404A (en) * | 1980-02-21 | 1983-05-31 | J. & P. Coats, Limited | Device and method for use in the treatment of damaged articular surfaces of human joints |
US4502161A (en) * | 1981-09-21 | 1985-03-05 | Wall W H | Prosthetic meniscus for the repair of joints |
US4636219A (en) * | 1985-12-05 | 1987-01-13 | Techmedica, Inc. | Prosthesis device fabrication |
US4644942A (en) * | 1981-07-27 | 1987-02-24 | Battelle Development Corporation | Production of porous coating on a prosthesis |
US4673408A (en) * | 1983-08-24 | 1987-06-16 | Arthroplasty Research & Development (Pty) Ltd. | Knee prosthesis |
US4714474A (en) * | 1986-05-12 | 1987-12-22 | Dow Corning Wright Corporation | Tibial knee joint prosthesis with removable articulating surface insert |
US4714473A (en) * | 1985-07-25 | 1987-12-22 | Harrington Arthritis Research Center | Knee prosthesis |
US4719908A (en) * | 1986-08-15 | 1988-01-19 | Osteonics Corp. | Method and apparatus for implanting a prosthetic device |
US4863538A (en) * | 1986-10-17 | 1989-09-05 | Board Of Regents, The University Of Texas System | Method and apparatus for producing parts by selective sintering |
US4944817A (en) * | 1986-10-17 | 1990-07-31 | Board Of Regents, The University Of Texas System | Multiple material systems for selective beam sintering |
US4961154A (en) * | 1986-06-03 | 1990-10-02 | Scitex Corporation Ltd. | Three dimensional modelling apparatus |
US4969907A (en) * | 1985-01-08 | 1990-11-13 | Sulzer Brothers Limited | Metal bone implant |
US4990163A (en) * | 1989-02-06 | 1991-02-05 | Trustees Of The University Of Pennsylvania | Method of depositing calcium phosphate cermamics for bone tissue calcification enhancement |
US5004476A (en) * | 1989-10-31 | 1991-04-02 | Tulane University | Porous coated total hip replacement system |
US5017753A (en) * | 1986-10-17 | 1991-05-21 | Board Of Regents, The University Of Texas System | Method and apparatus for producing parts by selective sintering |
US5024670A (en) * | 1989-10-02 | 1991-06-18 | Depuy, Division Of Boehringer Mannheim Corporation | Polymeric bearing component |
US5031120A (en) * | 1987-12-23 | 1991-07-09 | Itzchak Pomerantz | Three dimensional modelling apparatus |
US5034186A (en) * | 1985-11-20 | 1991-07-23 | Permelec Electrode Ltd. | Process for providing titanium composite having a porous surface |
US5053090A (en) * | 1989-09-05 | 1991-10-01 | Board Of Regents, The University Of Texas System | Selective laser sintering with assisted powder handling |
US5067964A (en) * | 1989-12-13 | 1991-11-26 | Stryker Corporation | Articular surface repair |
US5076869A (en) * | 1986-10-17 | 1991-12-31 | Board Of Regents, The University Of Texas System | Multiple material systems for selective beam sintering |
US5080674A (en) * | 1988-09-08 | 1992-01-14 | Zimmer, Inc. | Attachment mechanism for securing an additional portion to an implant |
US5108432A (en) * | 1990-06-24 | 1992-04-28 | Pfizer Hospital Products Group, Inc. | Porous fixation surface |
US5147402A (en) * | 1990-12-05 | 1992-09-15 | Sulzer Brothers Limited | Implant for ingrowth of osseous tissue |
US5155324A (en) * | 1986-10-17 | 1992-10-13 | Deckard Carl R | Method for selective laser sintering with layerwise cross-scanning |
US5158574A (en) * | 1987-07-20 | 1992-10-27 | Regen Corporation | Prosthetic meniscus |
US5171282A (en) * | 1990-01-12 | 1992-12-15 | Societe Civile D'innovations Technologique | Femoral member for knee prosthesis |
US5176710A (en) * | 1991-01-23 | 1993-01-05 | Orthopaedic Research Institute | Prosthesis with low stiffness factor |
US5192328A (en) * | 1989-09-29 | 1993-03-09 | Winters Thomas F | Knee joint replacement apparatus |
US5219362A (en) * | 1991-02-07 | 1993-06-15 | Finsbury (Instruments) Limited | Knee prosthesis |
US5282870A (en) * | 1992-01-14 | 1994-02-01 | Sulzer Medizinaltechnik Ag | Artificial knee joint |
US5282861A (en) * | 1992-03-11 | 1994-02-01 | Ultramet | Open cell tantalum structures for cancellous bone implants and cell and tissue receptors |
US5287435A (en) * | 1987-06-02 | 1994-02-15 | Cubital Ltd. | Three dimensional modeling |
US5314478A (en) * | 1991-03-29 | 1994-05-24 | Kyocera Corporation | Artificial bone connection prosthesis |
US5323954A (en) * | 1990-12-21 | 1994-06-28 | Zimmer, Inc. | Method of bonding titanium to a cobalt-based alloy substrate in an orthophedic implant device |
US5358529A (en) * | 1993-03-05 | 1994-10-25 | Smith & Nephew Richards Inc. | Plastic knee femoral implants |
US5368602A (en) * | 1993-02-11 | 1994-11-29 | De La Torre; Roger A. | Surgical mesh with semi-rigid border members |
US5386500A (en) * | 1987-06-02 | 1995-01-31 | Cubital Ltd. | Three dimensional modeling apparatus |
US5398193A (en) * | 1993-08-20 | 1995-03-14 | Deangelis; Alfredo O. | Method of three-dimensional rapid prototyping through controlled layerwise deposition/extraction and apparatus therefor |
US5443510A (en) * | 1993-04-06 | 1995-08-22 | Zimmer, Inc. | Porous coated implant and method of making same |
US5443518A (en) * | 1993-07-20 | 1995-08-22 | Zimmer, Inc. | Knee position indicator |
US5490962A (en) * | 1993-10-18 | 1996-02-13 | Massachusetts Institute Of Technology | Preparation of medical devices by solid free-form fabrication methods |
US5496372A (en) * | 1992-04-17 | 1996-03-05 | Kyocera Corporation | Hard tissue prosthesis including porous thin metal sheets |
US5504300A (en) * | 1994-04-18 | 1996-04-02 | Zimmer, Inc. | Orthopaedic implant and method of making same |
US5514183A (en) * | 1994-12-20 | 1996-05-07 | Epstein; Norman | Reduced friction prosthetic knee joint utilizing replaceable roller bearings |
US5549700A (en) * | 1993-09-07 | 1996-08-27 | Ortho Development Corporation | Segmented prosthetic articulation |
US5571185A (en) * | 1991-10-12 | 1996-11-05 | Eska Implants Gmbh | Process for the production of a bone implant and a bone implant produced thereby |
US5571196A (en) * | 1994-10-24 | 1996-11-05 | Stein; Daniel | Patello-femoral joint replacement device and method |
US5609646A (en) * | 1992-01-23 | 1997-03-11 | Howmedica International | Acetabular cup for a total hip prosthesis |
US5616294A (en) * | 1986-10-17 | 1997-04-01 | Board Of Regents, The University Of Texas System | Method for producing parts by infiltration of porous intermediate parts |
US5640667A (en) * | 1995-11-27 | 1997-06-17 | Board Of Regents, The University Of Texas System | Laser-directed fabrication of full-density metal articles using hot isostatic processing |
US5648450A (en) * | 1992-11-23 | 1997-07-15 | Dtm Corporation | Sinterable semi-crystalline powder and near-fully dense article formed therein |
US5681354A (en) * | 1996-02-20 | 1997-10-28 | Board Of Regents, University Of Colorado | Asymmetrical femoral component for knee prosthesis |
US5702448A (en) * | 1990-09-17 | 1997-12-30 | Buechel; Frederick F. | Prosthesis with biologically inert wear resistant surface |
US5728162A (en) * | 1993-01-28 | 1998-03-17 | Board Of Regents Of University Of Colorado | Asymmetric condylar and trochlear femoral knee component |
US5735903A (en) * | 1987-07-20 | 1998-04-07 | Li; Shu-Tung | Meniscal augmentation device |
US5773789A (en) * | 1994-04-18 | 1998-06-30 | Bristol-Myers Squibb Company | Method of making an orthopaedic implant having a porous metal pad |
US5776201A (en) * | 1995-10-02 | 1998-07-07 | Johnson & Johnson Professional, Inc. | Modular femoral trial system |
US5782908A (en) * | 1995-08-22 | 1998-07-21 | Medtronic, Inc. | Biocompatible medical article and method |
US5795353A (en) * | 1994-05-06 | 1998-08-18 | Advanced Bio Surfaces, Inc. | Joint resurfacing system |
US5824098A (en) * | 1994-10-24 | 1998-10-20 | Stein; Daniel | Patello-femoral joint replacement device and method |
US5824102A (en) * | 1992-06-19 | 1998-10-20 | Buscayret; Christian | Total knee prosthesis |
US5879398A (en) * | 1995-02-14 | 1999-03-09 | Zimmer, Inc. | Acetabular cup |
US5879387A (en) * | 1994-08-25 | 1999-03-09 | Howmedica International Inc. | Prosthetic bearing element and method of manufacture |
US5928285A (en) * | 1997-05-30 | 1999-07-27 | Bristol-Myers Squibb Co. | Orthopaedic implant having an articulating surface with a conforming and translational surface |
US5973222A (en) * | 1994-04-18 | 1999-10-26 | Bristol-Myers Squibb Co. | Orthopedic implant having a porous metal pad |
US5989472A (en) * | 1994-10-05 | 1999-11-23 | Howmedica International, Inc. | Method for making a reinforced orthopedic implant |
US6046426A (en) * | 1996-07-08 | 2000-04-04 | Sandia Corporation | Method and system for producing complex-shape objects |
US6049054A (en) * | 1994-04-18 | 2000-04-11 | Bristol-Myers Squibb Company | Method of making an orthopaedic implant having a porous metal pad |
US6087553A (en) * | 1996-02-26 | 2000-07-11 | Implex Corporation | Implantable metallic open-celled lattice/polyethylene composite material and devices |
US6096043A (en) * | 1998-12-18 | 2000-08-01 | Depuy Orthopaedics, Inc. | Epicondylar axis alignment-femoral positioning drill guide |
US6132468A (en) * | 1998-09-10 | 2000-10-17 | Mansmann; Kevin A. | Arthroscopic replacement of cartilage using flexible inflatable envelopes |
US6139585A (en) * | 1998-03-11 | 2000-10-31 | Depuy Orthopaedics, Inc. | Bioactive ceramic coating and method |
US6190407B1 (en) * | 1997-11-20 | 2001-02-20 | St. Jude Medical, Inc. | Medical article with adhered antimicrobial metal |
US6206927B1 (en) * | 1999-04-02 | 2001-03-27 | Barry M. Fell | Surgically implantable knee prothesis |
US6206924B1 (en) * | 1999-10-20 | 2001-03-27 | Interpore Cross Internat | Three-dimensional geometric bio-compatible porous engineered structure for use as a bone mass replacement or fusion augmentation device |
US6215093B1 (en) * | 1996-12-02 | 2001-04-10 | Fraunhofer-Gesellschaft Zur Foerderung Der Angewandten Forschung E.V. | Selective laser sintering at melting temperature |
US6248131B1 (en) * | 1994-05-06 | 2001-06-19 | Advanced Bio Surfaces, Inc. | Articulating joint repair |
US6251143B1 (en) * | 1999-06-04 | 2001-06-26 | Depuy Orthopaedics, Inc. | Cartilage repair unit |
US6261322B1 (en) * | 1998-05-14 | 2001-07-17 | Hayes Medical, Inc. | Implant with composite coating |
US20010014403A1 (en) * | 1997-08-12 | 2001-08-16 | Lawrence Evans Brown | Method and apparatus for making components by direct laser processing |
US6280478B1 (en) * | 1997-03-04 | 2001-08-28 | Implico B.V. | Artefact suitable for use as a bone implant |
US6283997B1 (en) * | 1998-11-13 | 2001-09-04 | The Trustees Of Princeton University | Controlled architecture ceramic composites by stereolithography |
US6299645B1 (en) * | 1999-07-23 | 2001-10-09 | William S. Ogden | Dove tail total knee replacement unicompartmental |
US6371958B1 (en) * | 2000-03-02 | 2002-04-16 | Ethicon, Inc. | Scaffold fixation device for use in articular cartilage repair |
US6395327B1 (en) * | 1999-03-12 | 2002-05-28 | Zimmer, Inc. | Enhanced fatigue strength orthopaedic implant with porous coating and method of making same |
Family Cites Families (305)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US222687A (en) * | 1879-12-16 | Improvement in combined pencil and line-measurer | ||
US2222687A (en) | 1936-05-08 | 1940-11-26 | Maiden Form Brassiere Company | Strap construction |
US2373769A (en) | 1942-08-17 | 1945-04-17 | Claude W Macy | Tire repairing device |
US3520099A (en) * | 1968-09-16 | 1970-07-14 | Mastic Corp | Interlocking building siding unit |
US3556918A (en) * | 1968-12-03 | 1971-01-19 | Jerome H Lemelson | Composite reinforced plastic foam sheet |
US3826054A (en) * | 1972-05-15 | 1974-07-30 | B Culpepper | Building insulation and sheathing |
FR2214460B1 (en) | 1973-01-18 | 1976-05-14 | Ceraver | |
US3906550A (en) | 1973-12-27 | 1975-09-23 | William Rostoker | Prosthetic device having a porous fiber metal structure |
US4117302A (en) | 1974-03-04 | 1978-09-26 | Caterpillar Tractor Co. | Method for fusibly bonding a coating material to a metal article |
US4073999A (en) | 1975-05-09 | 1978-02-14 | Minnesota Mining And Manufacturing Company | Porous ceramic or metallic coatings and articles |
US4047349A (en) | 1976-05-14 | 1977-09-13 | Johns-Manville Corporation | Sheet material attaching device and wall arrangement using this device |
US4259072A (en) | 1977-04-04 | 1981-03-31 | Kyoto Ceramic Co., Ltd. | Ceramic endosseous implant |
US4154040A (en) * | 1978-02-24 | 1979-05-15 | Pace Thomas G | Building siding and beveled backer panel assembly and method |
US4247508B1 (en) | 1979-12-03 | 1996-10-01 | Dtm Corp | Molding process |
US4479271A (en) | 1981-10-26 | 1984-10-30 | Zimmer, Inc. | Prosthetic device adapted to promote bone/tissue ingrowth |
JPS58132068A (en) * | 1982-01-30 | 1983-08-06 | Nitto Electric Ind Co Ltd | Reinforcing adhesive sheet |
CA1227002A (en) | 1982-02-18 | 1987-09-22 | Robert V. Kenna | Bone prosthesis with porous coating |
US4542539A (en) | 1982-03-12 | 1985-09-24 | Artech Corp. | Surgical implant having a graded porous coating |
US4474861A (en) | 1983-03-09 | 1984-10-02 | Smith International, Inc. | Composite bearing structure of alternating hard and soft metal, and process for making the same |
US4659331A (en) | 1983-11-28 | 1987-04-21 | Regents Of University Of Michigan | Prosthesis interface surface and method of implanting |
US4543158A (en) | 1984-04-02 | 1985-09-24 | Gaf Corporation | Sheet type felt |
US4513045A (en) * | 1984-04-02 | 1985-04-23 | Gaf Corporation | Sheet type felt |
US4673409A (en) | 1984-04-25 | 1987-06-16 | Minnesota Mining And Manufacturing Company | Implant with attachment surface |
CA1264674A (en) * | 1984-10-17 | 1990-01-23 | Paul Ducheyne | Porous flexible metal fiber material for surgical implantation |
CH665348A5 (en) | 1985-01-09 | 1988-05-13 | Sulzer Ag | IMPLANTS. |
US4969302A (en) | 1985-01-15 | 1990-11-13 | Abitibi-Price Corporation | Siding panels |
CH665770A5 (en) | 1985-01-25 | 1988-06-15 | Sulzer Ag | PLASTIC BONE IMPLANT. |
US5002572A (en) | 1986-09-11 | 1991-03-26 | Picha George J | Biological implant with textured surface |
US4766029A (en) | 1987-01-23 | 1988-08-23 | Kimberly-Clark Corporation | Semi-permeable nonwoven laminate |
US20020102674A1 (en) | 1987-05-20 | 2002-08-01 | David M Anderson | Stabilized microporous materials |
US4837067A (en) | 1987-06-08 | 1989-06-06 | Minnesota Mining And Manufacturing Company | Nonwoven thermal insulating batts |
US5306311A (en) | 1987-07-20 | 1994-04-26 | Regen Corporation | Prosthetic articular cartilage |
CH672985A5 (en) | 1987-11-11 | 1990-01-31 | Sulzer Ag | |
US4944756A (en) | 1988-02-03 | 1990-07-31 | Pfizer Hospital Products Group | Prosthetic knee joint with improved patellar component tracking |
JP2829318B2 (en) | 1988-06-10 | 1998-11-25 | 春幸 川原 | Frameless, coreless porous endosseous implant |
US5486599A (en) | 1989-03-29 | 1996-01-23 | The Board Of Trustees Of The Leland Stanford Junior University | Construction and use of synthetic constructs encoding syndecan |
JPH0813519B2 (en) | 1989-03-29 | 1996-02-14 | 東レ株式会社 | Glass fiber mat Insulation lining Metal origami shingles |
EP0425714A1 (en) | 1989-10-28 | 1991-05-08 | Metalpraecis Berchem + Schaberg Gesellschaft Für Metallformgebung Mbh | Process for manufacturing an implantable joint prosthesis |
GB8925380D0 (en) | 1989-11-09 | 1989-12-28 | Leonard Ian | Producing prostheses |
US4997445A (en) | 1989-12-08 | 1991-03-05 | Zimmer, Inc. | Metal-backed prosthetic implant with enhanced bonding of polyethylene portion to metal base |
JPH041794A (en) | 1990-04-19 | 1992-01-07 | Sakurai Kk | Adhesive sheet for display |
US5122116A (en) | 1990-04-24 | 1992-06-16 | Science Incorporated | Closed drug delivery system |
JPH0441794A (en) | 1990-06-01 | 1992-02-12 | Mitsubishi Paper Mills Ltd | Fiber sheet and its complex sheet |
US5108441A (en) | 1990-07-17 | 1992-04-28 | Mcdowell Charles L | Method of regenerating joint articular cartilage |
US5090174A (en) * | 1990-09-26 | 1992-02-25 | Fragale Anthony J | Siding system including siding trim pieces and method of siding a structure using same |
US5274565A (en) | 1990-10-03 | 1993-12-28 | Board Of Regents, The University Of Texas System | Process for making custom joint replacements |
US5258098A (en) | 1991-06-17 | 1993-11-02 | Cycam, Inc. | Method of production of a surface adapted to promote adhesion |
DE59108588D1 (en) | 1991-08-07 | 1997-04-10 | Oscobal Ag | Endoprosthesis with a metal wire |
US5356433A (en) | 1991-08-13 | 1994-10-18 | Cordis Corporation | Biocompatible metal surfaces |
DE4205969C2 (en) | 1992-02-27 | 1994-07-07 | Merck Patent Gmbh | Process for the production of moldings with a predetermined pore structure |
CA2075553A1 (en) * | 1992-08-07 | 1994-02-08 | George Zafir | Insulated panel |
US5510066A (en) | 1992-08-14 | 1996-04-23 | Guild Associates, Inc. | Method for free-formation of a free-standing, three-dimensional body |
US5370692A (en) | 1992-08-14 | 1994-12-06 | Guild Associates, Inc. | Rapid, customized bone prosthesis |
US5527877A (en) | 1992-11-23 | 1996-06-18 | Dtm Corporation | Sinterable semi-crystalline powder and near-fully dense article formed therewith |
US5336518A (en) | 1992-12-11 | 1994-08-09 | Cordis Corporation | Treatment of metallic surfaces using radiofrequency plasma deposition and chemical attachment of bioactive agents |
US5352405A (en) | 1992-12-18 | 1994-10-04 | Dtm Corporation | Thermal control of selective laser sintering via control of the laser scan |
US5380328A (en) * | 1993-08-09 | 1995-01-10 | Timesh, Inc. | Composite perforated implant structures |
DE69432023T2 (en) | 1993-09-10 | 2003-10-23 | Univ Queensland Santa Lucia | STEREOLITHOGRAPHIC ANATOMIC MODELING PROCESS |
US5518680A (en) * | 1993-10-18 | 1996-05-21 | Massachusetts Institute Of Technology | Tissue regeneration matrices by solid free form fabrication techniques |
DE4341367C1 (en) | 1993-12-04 | 1995-06-14 | Harald Dr Med Dr Med Eufinger | Process for the production of endoprostheses |
US6415574B2 (en) * | 1993-12-22 | 2002-07-09 | Certainteed Corp. | Reinforced exterior siding |
US5461839A (en) * | 1993-12-22 | 1995-10-31 | Certainteed Corporation | Reinforced exterior siding |
US5665118A (en) | 1994-02-18 | 1997-09-09 | Johnson & Johnson Professional, Inc. | Bone prostheses with direct cast macrotextured surface regions and method for manufacturing the same |
BE1008372A3 (en) | 1994-04-19 | 1996-04-02 | Materialise Nv | METHOD FOR MANUFACTURING A perfected MEDICAL MODEL BASED ON DIGITAL IMAGE INFORMATION OF A BODY. |
IL109344A (en) | 1994-04-19 | 1998-02-22 | Mendes David | Prosthetic patella implant of the knee joint |
US5857303A (en) * | 1994-05-13 | 1999-01-12 | Certainteed Corporation | Apparatus and method of applying building panels to surfaces |
US5729946A (en) * | 1994-05-13 | 1998-03-24 | Certainteed Corporation | Apparatus and method of applying building panels to surfaces |
US5639402A (en) | 1994-08-08 | 1997-06-17 | Barlow; Joel W. | Method for fabricating artificial bone implant green parts |
US6290726B1 (en) | 2000-01-30 | 2001-09-18 | Diamicron, Inc. | Prosthetic hip joint having sintered polycrystalline diamond compact articulation surfaces |
US7494507B2 (en) | 2000-01-30 | 2009-02-24 | Diamicron, Inc. | Articulating diamond-surfaced spinal implants |
US5632745A (en) | 1995-02-07 | 1997-05-27 | R&D Biologicals, Inc. | Surgical implantation of cartilage repair unit |
US5769899A (en) | 1994-08-12 | 1998-06-23 | Matrix Biotechnologies, Inc. | Cartilage repair unit |
DE19502733A1 (en) | 1994-09-20 | 1996-03-21 | Gefinex Jackon Gmbh | Tiling panel for interiors |
US5716358A (en) | 1994-12-02 | 1998-02-10 | Johnson & Johnson Professional, Inc. | Directional bone fixation device |
US5489306A (en) | 1995-01-03 | 1996-02-06 | Gorski; Jerrold M. | Graduated porosity implant for fibro-osseous integration |
US6051751A (en) | 1995-01-20 | 2000-04-18 | Spire Corporation | Arthroplasty process for securely anchoring prostheses to bone, and arthroplasty products therefor |
US5749874A (en) | 1995-02-07 | 1998-05-12 | Matrix Biotechnologies, Inc. | Cartilage repair unit and method of assembling same |
DE19511772C2 (en) | 1995-03-30 | 1997-09-04 | Eos Electro Optical Syst | Device and method for producing a three-dimensional object |
US6149688A (en) | 1995-06-07 | 2000-11-21 | Surgical Dynamics, Inc. | Artificial bone graft implant |
US6209621B1 (en) | 1995-07-07 | 2001-04-03 | Depuy Orthopaedics, Inc. | Implantable prostheses with metallic porous bead preforms applied during casting and method of forming the same |
EP0761242A1 (en) | 1995-08-21 | 1997-03-12 | Bristol-Myers Squibb Company | Orthopaedic implant with bearing surface |
US6149689A (en) | 1995-11-22 | 2000-11-21 | Eska Implants Gmbh & Co. | Implant as bone replacement |
US5769092A (en) | 1996-02-22 | 1998-06-23 | Integrated Surgical Systems, Inc. | Computer-aided system for revision total hip replacement surgery |
US6143948A (en) | 1996-05-10 | 2000-11-07 | Isotis B.V. | Device for incorporation and release of biologically active agents |
AU2759397A (en) | 1996-05-28 | 1998-01-05 | 1218122 Ontario Inc. | Resorbable implant biomaterial made of condensed calcium phosphate particles |
US5811151A (en) | 1996-05-31 | 1998-09-22 | Medtronic, Inc. | Method of modifying the surface of a medical device |
US6476343B2 (en) | 1996-07-08 | 2002-11-05 | Sandia Corporation | Energy-beam-driven rapid fabrication system |
US6013855A (en) | 1996-08-06 | 2000-01-11 | United States Surgical | Grafting of biocompatible hydrophilic polymers onto inorganic and metal surfaces |
US5989269A (en) | 1996-08-30 | 1999-11-23 | Vts Holdings L.L.C. | Method, instruments and kit for autologous transplantation |
US7332537B2 (en) | 1996-09-04 | 2008-02-19 | Z Corporation | Three dimensional printing material system and method |
GB2318058B (en) | 1996-09-25 | 2001-03-21 | Ninian Spenceley Peckitt | Improvements relating to prosthetic implants |
US6530951B1 (en) * | 1996-10-24 | 2003-03-11 | Cook Incorporated | Silver implantable medical device |
US6128866A (en) | 1996-11-08 | 2000-10-10 | Wearne; John R. | Identifying prefabricated exterior siding and related trim items |
US6261493B1 (en) * | 1997-03-20 | 2001-07-17 | Therics, Inc. | Fabrication of tissue products with additives by casting or molding using a mold formed by solid free-form methods |
US6240616B1 (en) | 1997-04-15 | 2001-06-05 | Advanced Cardiovascular Systems, Inc. | Method of manufacturing a medicated porous metal prosthesis |
BE1011244A3 (en) | 1997-06-30 | 1999-06-01 | Bekaert Sa Nv | LAYERED TUBULAR METAL STRUCTURE. |
US6045581A (en) | 1997-12-12 | 2000-04-04 | Sulzer Orthopedics Inc. | Implantable prosthesis having textured bearing surfaces |
US6208959B1 (en) * | 1997-12-15 | 2001-03-27 | Telefonaktibolaget Lm Ericsson (Publ) | Mapping of digital data symbols onto one or more formant frequencies for transmission over a coded voice channel |
WO1999033641A1 (en) | 1997-12-24 | 1999-07-08 | Molecular Geodesics, Inc. | Foam scaffold materials |
US6171340B1 (en) | 1998-02-27 | 2001-01-09 | Mcdowell Charles L. | Method and device for regenerating cartilage in articulating joints |
JPH11287020A (en) | 1998-04-03 | 1999-10-19 | Ig Tech Res Inc | Soundproof exterior finish material |
US20010008674A1 (en) | 1998-05-23 | 2001-07-19 | Ralph Smith | Underlayment mat employed with a single ply roofing system |
JPH11348045A (en) | 1998-06-10 | 1999-12-21 | Matsushita Electric Ind Co Ltd | Metal mold |
US6774071B2 (en) * | 1998-09-08 | 2004-08-10 | Building Materials Investment Corporation | Foamed facer and insulation boards made therefrom |
US6350284B1 (en) | 1998-09-14 | 2002-02-26 | Bionx Implants, Oy | Bioabsorbable, layered composite material for guided bone tissue regeneration |
AU768641B2 (en) | 1998-10-12 | 2003-12-18 | Massachusetts Institute Of Technology | Composites for tissue regeneration and methods of manufacture thereof |
US7343960B1 (en) | 1998-11-20 | 2008-03-18 | Rolls-Royce Corporation | Method and apparatus for production of a cast component |
DE19901643A1 (en) * | 1999-01-19 | 2000-07-20 | Herbst Bremer Goldschlaegerei | Process for the production of dentures and dental auxiliary parts |
US20020187458A1 (en) | 1999-01-19 | 2002-12-12 | Bego Bremer Goldschlagerei Wilh. Herbst Gmbh & Co. | Method for producing tooth replacements and auxiliary dental parts |
RU2218242C2 (en) | 1999-02-11 | 2003-12-10 | Физический институт им. П.Н. Лебедева РАН | Method for making medical implants from biologically compatible materials |
US6206883B1 (en) * | 1999-03-05 | 2001-03-27 | Stryker Technologies Corporation | Bioabsorbable materials and medical devices made therefrom |
US6558421B1 (en) * | 2000-09-19 | 2003-05-06 | Barry M. Fell | Surgically implantable knee prosthesis |
US7341602B2 (en) * | 1999-05-10 | 2008-03-11 | Fell Barry M | Proportioned surgically implantable knee prosthesis |
US6582715B1 (en) | 1999-04-27 | 2003-06-24 | Agion Technologies, Inc. | Antimicrobial orthopedic implants |
US6370382B1 (en) * | 1999-04-27 | 2002-04-09 | Qualcomm Incorporated | System and method for reducing wireless telecommunications network resources required to successfully route calls to a wireline network |
US7338524B2 (en) | 1999-05-10 | 2008-03-04 | Fell Barry M | Surgically implantable knee prosthesis |
US6855165B2 (en) * | 1999-05-10 | 2005-02-15 | Barry M. Fell | Surgically implantable knee prosthesis having enlarged femoral surface |
US6893463B2 (en) * | 1999-05-10 | 2005-05-17 | Barry M. Fell | Surgically implantable knee prosthesis having two-piece keyed components |
US7491235B2 (en) | 1999-05-10 | 2009-02-17 | Fell Barry M | Surgically implantable knee prosthesis |
US6966928B2 (en) * | 1999-05-10 | 2005-11-22 | Fell Barry M | Surgically implantable knee prosthesis having keels |
US7297161B2 (en) | 1999-05-10 | 2007-11-20 | Fell Barry M | Surgically implantable knee prosthesis |
US6923831B2 (en) * | 1999-05-10 | 2005-08-02 | Barry M. Fell | Surgically implantable knee prosthesis having attachment apertures |
US6911044B2 (en) * | 1999-05-10 | 2005-06-28 | Barry M. Fell | Surgically implantable knee prosthesis having medially shifted tibial surface |
US6866684B2 (en) * | 1999-05-10 | 2005-03-15 | Barry M. Fell | Surgically implantable knee prosthesis having different tibial and femoral surface profiles |
US20050033424A1 (en) * | 1999-05-10 | 2005-02-10 | Fell Barry M. | Surgically implantable knee prosthesis |
US6520996B1 (en) * | 1999-06-04 | 2003-02-18 | Depuy Acromed, Incorporated | Orthopedic implant |
US6811744B2 (en) * | 1999-07-07 | 2004-11-02 | Optomec Design Company | Forming structures from CAD solid models |
US6702848B1 (en) | 1999-07-20 | 2004-03-09 | Peter Paul Zilla | Foam-type vascular prosthesis with well-defined anclio-permissive open porosity |
US6368354B2 (en) | 1999-10-07 | 2002-04-09 | Exactech, Inc. | Acetabular bearing assembly for total hip joints |
JP2003512110A (en) | 1999-10-15 | 2003-04-02 | マウント・シナイ・ホスピタル | Synthetic substrate for tissue formation |
JP2003518193A (en) | 1999-11-16 | 2003-06-03 | トリトン・システムズ・インコーポレイテツド | Laser processing of discontinuous reinforced metal matrix composites |
FR2801193B1 (en) | 1999-11-19 | 2002-02-15 | Proconcept | DOUBLE MOBILITY EXPANDABLE COTYLOIDAL PROSTHESIS |
US20040009228A1 (en) | 1999-11-30 | 2004-01-15 | Pertti Tormala | Bioabsorbable drug delivery system for local treatment and prevention of infections |
US7115143B1 (en) | 1999-12-08 | 2006-10-03 | Sdgi Holdings, Inc. | Orthopedic implant surface configuration |
US20050203630A1 (en) | 2000-01-30 | 2005-09-15 | Pope Bill J. | Prosthetic knee joint having at least one diamond articulation surface |
KR100358192B1 (en) | 2000-02-16 | 2002-10-25 | 한국과학기술원 | Jacket for cementless artificial joint and the artificial joint with it |
US6551608B2 (en) | 2000-03-06 | 2003-04-22 | Porex Technologies Corporation | Porous plastic media with antiviral or antimicrobial properties and processes for making the same |
US6626945B2 (en) | 2000-03-14 | 2003-09-30 | Chondrosite, Llc | Cartilage repair plug |
US6632246B1 (en) | 2000-03-14 | 2003-10-14 | Chondrosite, Llc | Cartilage repair plug |
US6712856B1 (en) * | 2000-03-17 | 2004-03-30 | Kinamed, Inc. | Custom replacement device for resurfacing a femur and method of making the same |
EP1312025A2 (en) * | 2000-04-05 | 2003-05-21 | Therics, Inc. | System and method for rapidly customizing a design and remotely manufacturing biomedical devices using a computer system |
US6772026B2 (en) | 2000-04-05 | 2004-08-03 | Therics, Inc. | System and method for rapidly customizing design, manufacture and/or selection of biomedical devices |
ITVI20000025U1 (en) * | 2000-04-07 | 2001-10-07 | Tecres Spa | TEMPORARY SPACER DEVICE FOR SURGICAL TREATMENT OF THE KNEE |
TW462510U (en) | 2000-04-24 | 2001-11-01 | Delta Electronics Inc | Hanged-type eccentric fan |
JP4465802B2 (en) | 2000-04-25 | 2010-05-26 | 日東紡績株式会社 | Siding panel and outer wall panel using the same |
AU2001259327B2 (en) | 2000-05-01 | 2005-02-17 | Arthrosurface, Inc. | System and method for joint resurface repair |
US7618462B2 (en) | 2000-05-01 | 2009-11-17 | Arthrosurface Incorporated | System and method for joint resurface repair |
US6610067B2 (en) | 2000-05-01 | 2003-08-26 | Arthrosurface, Incorporated | System and method for joint resurface repair |
US7163541B2 (en) | 2002-12-03 | 2007-01-16 | Arthrosurface Incorporated | Tibial resurfacing system |
US20040230315A1 (en) | 2000-05-01 | 2004-11-18 | Ek Steven W. | Articular surface implant |
US6679917B2 (en) | 2000-05-01 | 2004-01-20 | Arthrosurface, Incorporated | System and method for joint resurface repair |
WO2001092001A1 (en) | 2000-05-26 | 2001-12-06 | University Of Virginia Patent Foundation | Multifunctional periodic cellular solids and the method of making thereof |
US6676892B2 (en) * | 2000-06-01 | 2004-01-13 | Board Of Regents, University Texas System | Direct selective laser sintering of metals |
US20020130112A1 (en) | 2000-06-05 | 2002-09-19 | Mark Manasas | Orthopedic implant and method of making metal articles |
JP3679315B2 (en) * | 2000-07-19 | 2005-08-03 | 経憲 武井 | Knee prosthesis |
JP2004521666A (en) | 2000-08-28 | 2004-07-22 | アドバンスト バイオ サーフェイシズ,インコーポレイティド | Methods and systems for enhancing mammalian joints |
US20020062154A1 (en) | 2000-09-22 | 2002-05-23 | Ayers Reed A. | Non-uniform porosity tissue implant |
DE10057675C2 (en) * | 2000-11-21 | 2003-02-13 | Andrej Nowakowski | Knee endoprosthesis |
US6494914B2 (en) | 2000-12-05 | 2002-12-17 | Biomet, Inc. | Unicondylar femoral prosthesis and instruments |
US6599323B2 (en) | 2000-12-21 | 2003-07-29 | Ethicon, Inc. | Reinforced tissue implants and methods of manufacture and use |
ATE387161T1 (en) | 2001-01-25 | 2008-03-15 | Smith & Nephew Inc | RETAINING DEVICE FOR HOLDING A PROSTHETIC COMPONENT |
US6599322B1 (en) | 2001-01-25 | 2003-07-29 | Tecomet, Inc. | Method for producing undercut micro recesses in a surface, a surgical implant made thereby, and method for fixing an implant to bone |
US9050192B2 (en) | 2001-02-05 | 2015-06-09 | Formae, Inc. | Cartilage repair implant with soft bearing surface and flexible anchoring device |
US6863689B2 (en) | 2001-07-16 | 2005-03-08 | Spinecore, Inc. | Intervertebral spacer having a flexible wire mesh vertebral body contact element |
EP1362129A1 (en) | 2001-02-19 | 2003-11-19 | IsoTis N.V. | Porous metals and metal coatings for implants |
US7597715B2 (en) | 2005-04-21 | 2009-10-06 | Biomet Manufacturing Corp. | Method and apparatus for use of porous implants |
US6743232B2 (en) | 2001-02-26 | 2004-06-01 | David W. Overaker | Tissue scaffold anchor for cartilage repair |
EP1247537A1 (en) | 2001-04-04 | 2002-10-09 | Isotis B.V. | Coating for medical devices |
EP1379287A1 (en) | 2001-04-12 | 2004-01-14 | Therics, Inc. | Method and apparatus for engineered regenerative biostructures |
US6699252B2 (en) * | 2001-04-17 | 2004-03-02 | Regeneration Technologies, Inc. | Methods and instruments for improved meniscus transplantation |
WO2002085246A2 (en) | 2001-04-19 | 2002-10-31 | Case Western Reserve University | Fabrication of a polymeric prosthetic implant |
US6589283B1 (en) | 2001-05-15 | 2003-07-08 | Biomet, Inc. | Elongated femoral component |
US6482209B1 (en) | 2001-06-14 | 2002-11-19 | Gerard A. Engh | Apparatus and method for sculpting the surface of a joint |
US7174282B2 (en) | 2001-06-22 | 2007-02-06 | Scott J Hollister | Design methodology for tissue engineering scaffolds and biomaterial implants |
JP3646162B2 (en) | 2001-07-04 | 2005-05-11 | 独立行政法人産業技術総合研究所 | Transplant for cartilage tissue regeneration |
WO2003013338A2 (en) * | 2001-08-07 | 2003-02-20 | Depuy Orthopaedic, Inc | Patello-femoral joint arthroplasty |
GB0119652D0 (en) | 2001-08-11 | 2001-10-03 | Stanmore Implants Worldwide | Surgical implant |
US6850125B2 (en) * | 2001-08-15 | 2005-02-01 | Gallitzin Allegheny Llc | Systems and methods for self-calibration |
US6749639B2 (en) * | 2001-08-27 | 2004-06-15 | Mayo Foundation For Medical Education And Research | Coated prosthetic implant |
US6682567B1 (en) | 2001-09-19 | 2004-01-27 | Biomet, Inc. | Method and apparatus for providing a shell component incorporating a porous ingrowth material and liner |
US20030060113A1 (en) | 2001-09-20 | 2003-03-27 | Christie Peter A. | Thermo formable acoustical panel |
JP4330991B2 (en) * | 2001-10-01 | 2009-09-16 | スキャンディウス・バイオメディカル・インコーポレーテッド | Apparatus and method for repairing articular cartilage defects |
US6686437B2 (en) * | 2001-10-23 | 2004-02-03 | M.M.A. Tech Ltd. | Medical implants made of wear-resistant, high-performance polyimides, process of making same and medical use of same |
FR2831426B1 (en) | 2001-10-30 | 2004-07-16 | Tornier Sa | JOINT IMPLANT AND KNEE PROSTHESIS INCORPORATING SUCH AN IMPLANT |
US6709462B2 (en) * | 2002-01-11 | 2004-03-23 | Mayo Foundation For Medical Education And Research | Acetabular shell with screw access channels |
US6966932B1 (en) | 2002-02-05 | 2005-11-22 | Biomet, Inc. | Composite acetabular component |
US7458991B2 (en) | 2002-02-08 | 2008-12-02 | Howmedica Osteonics Corp. | Porous metallic scaffold for tissue ingrowth |
JP3781186B2 (en) | 2002-02-13 | 2006-05-31 | 徹 勝呂 | Knee prosthesis |
US6740186B2 (en) | 2002-02-20 | 2004-05-25 | Zimmer Technology, Inc. | Method of making an orthopeadic implant having a porous metal surface |
EP1476097A4 (en) | 2002-02-20 | 2010-12-08 | Zimmer Inc | Knee arthroplasty prosthesis and method |
GB0204381D0 (en) * | 2002-02-26 | 2002-04-10 | Mcminn Derek J W | Knee prosthesis |
US20030220696A1 (en) | 2002-05-23 | 2003-11-27 | Levine David Jerome | Implantable porous metal |
US7918382B2 (en) | 2002-06-18 | 2011-04-05 | Zimmer Technology, Inc. | Method for attaching a porous metal layer to a metal substrate |
US20040006393A1 (en) | 2002-07-03 | 2004-01-08 | Brian Burkinshaw | Implantable prosthetic knee for lateral compartment |
AU2003249310A1 (en) * | 2002-07-17 | 2004-02-02 | Proxy Biomedical Limited | Soft tissue implants and methods for making same |
US20050103765A1 (en) * | 2002-07-31 | 2005-05-19 | Akira Kawasaki | Method and device for forming a body having a three-dimensional structure |
US7618907B2 (en) * | 2002-08-02 | 2009-11-17 | Owens Corning Intellectual Capital, Llc | Low porosity facings for acoustic applications |
DE60322066D1 (en) | 2002-08-15 | 2008-08-21 | Hfsc Co | BAND DISC IMPLANT |
US7008226B2 (en) | 2002-08-23 | 2006-03-07 | Woodwelding Ag | Implant, in particular a dental implant |
US20060106419A1 (en) | 2002-08-23 | 2006-05-18 | Peter Gingras | Three dimensional implant |
US20040054416A1 (en) * | 2002-09-12 | 2004-03-18 | Joe Wyss | Posterior stabilized knee with varus-valgus constraint |
GB2393625C (en) | 2002-09-26 | 2004-08-18 | Meridian Tech Ltd | Orthopaedic surgery planning |
US7637942B2 (en) | 2002-11-05 | 2009-12-29 | Merit Medical Systems, Inc. | Coated stent with geometry determinated functionality and method of making the same |
EP1418013B1 (en) | 2002-11-08 | 2005-01-19 | Howmedica Osteonics Corp. | Laser-produced porous surface |
US20060147332A1 (en) | 2004-12-30 | 2006-07-06 | Howmedica Osteonics Corp. | Laser-produced porous structure |
US20050070989A1 (en) | 2002-11-13 | 2005-03-31 | Whye-Kei Lye | Medical devices having porous layers and methods for making the same |
US6770099B2 (en) * | 2002-11-19 | 2004-08-03 | Zimmer Technology, Inc. | Femoral prosthesis |
JP3927487B2 (en) | 2002-12-02 | 2007-06-06 | 株式会社大野興業 | Manufacturing method of artificial bone model |
US6878427B2 (en) * | 2002-12-20 | 2005-04-12 | Kimberly Clark Worldwide, Inc. | Encased insulation article |
US7160330B2 (en) | 2003-01-21 | 2007-01-09 | Howmedica Osteonics Corp. | Emulating natural knee kinematics in a knee prosthesis |
US6994730B2 (en) | 2003-01-31 | 2006-02-07 | Howmedica Osteonics Corp. | Meniscal and tibial implants |
US6916341B2 (en) | 2003-02-20 | 2005-07-12 | Lindsey R. Rolston | Device and method for bicompartmental arthroplasty |
US20040167632A1 (en) | 2003-02-24 | 2004-08-26 | Depuy Products, Inc. | Metallic implants having roughened surfaces and methods for producing the same |
JP4239652B2 (en) | 2003-03-31 | 2009-03-18 | パナソニック電工株式会社 | Surface finishing method for metal powder sintered parts |
US7364590B2 (en) | 2003-04-08 | 2008-04-29 | Thomas Siebel | Anatomical knee prosthesis |
BRPI0409487A (en) | 2003-04-16 | 2006-05-02 | Porex Surgical Inc | surgical implant, process for its preparation and method of reconstruction of a bone defect |
US6993406B1 (en) | 2003-04-24 | 2006-01-31 | Sandia Corporation | Method for making a bio-compatible scaffold |
BRPI0410324A (en) * | 2003-05-15 | 2006-05-23 | Biomerix Corp | implantable device, elastomeric matrix production lyophilization processes having a cross-linked structure, polymerization for cross-linked elastomeric matrix preparation and cross-linked composite elastomeric implant preparation, and method for treating an orthopedic disorder |
AU2004238026A1 (en) | 2003-05-16 | 2004-11-25 | Cinvention Ag | Medical implants comprising biocompatible coatings |
WO2004110309A2 (en) | 2003-06-11 | 2004-12-23 | Case Western Reserve University | Computer-aided-design of skeletal implants |
US20040262809A1 (en) | 2003-06-30 | 2004-12-30 | Smith Todd S. | Crosslinked polymeric composite for orthopaedic implants |
EP1648348B1 (en) | 2003-07-24 | 2015-06-17 | Tecomet Inc. | Assembled non-random foams |
US20050085922A1 (en) | 2003-10-17 | 2005-04-21 | Shappley Ben R. | Shaped filler for implantation into a bone void and methods of manufacture and use thereof |
GB0325647D0 (en) | 2003-11-03 | 2003-12-10 | Finsbury Dev Ltd | Prosthetic implant |
PL1687133T3 (en) | 2003-11-04 | 2011-05-31 | Porex Corp | Composite porous materials and methods of making and using the same |
US20050100578A1 (en) * | 2003-11-06 | 2005-05-12 | Schmid Steven R. | Bone and tissue scaffolding and method for producing same |
US7001672B2 (en) | 2003-12-03 | 2006-02-21 | Medicine Lodge, Inc. | Laser based metal deposition of implant structures |
US7294149B2 (en) | 2003-12-05 | 2007-11-13 | Howmedica Osteonics Corp. | Orthopedic implant with angled pegs |
CN1972646B (en) | 2004-01-12 | 2010-05-26 | 德普伊产品公司 | Systems and methods for compartmental replacement in a knee |
WO2005069957A2 (en) | 2004-01-20 | 2005-08-04 | Alexander Michalow | Unicondylar knee implant |
US7189263B2 (en) | 2004-02-03 | 2007-03-13 | Vita Special Purpose Corporation | Biocompatible bone graft material |
US7442196B2 (en) | 2004-02-06 | 2008-10-28 | Synvasive Technology, Inc. | Dynamic knee balancer |
US7168283B2 (en) | 2004-02-09 | 2007-01-30 | Ast Acquisitions, Llc | Cobalt chrome forging of femoral knee implants and other components |
DE102004009126A1 (en) | 2004-02-25 | 2005-09-22 | Bego Medical Ag | Method and device for generating control data sets for the production of products by free-form sintering or melting and device for this production |
CA2557436A1 (en) | 2004-03-05 | 2005-09-29 | The Trustees Of Columbia University In The City Of New York | Polymer-ceramic-hydrogel composite scaffold for osteochondral repair |
GB0405680D0 (en) | 2004-03-13 | 2004-04-21 | Accentus Plc | Metal implants |
US7465318B2 (en) | 2004-04-15 | 2008-12-16 | Soteira, Inc. | Cement-directing orthopedic implants |
US7981942B2 (en) | 2004-06-07 | 2011-07-19 | Ticona Llc | Polyethylene molding powder and porous articles made therefrom |
WO2006007861A1 (en) | 2004-07-16 | 2006-01-26 | Universität Duisburg-Essen | Implant |
JP5154930B2 (en) | 2004-07-19 | 2013-02-27 | スミス アンド ネフュー インコーポレーテッド | Pulse electric current sintering method of the surface of a medical implant and the medical implant |
US20060036251A1 (en) | 2004-08-09 | 2006-02-16 | Reiley Mark A | Systems and methods for the fixation or fusion of bone |
US7351423B2 (en) | 2004-09-01 | 2008-04-01 | Depuy Spine, Inc. | Musculo-skeletal implant having a bioactive gradient |
GB0419961D0 (en) | 2004-09-08 | 2004-10-13 | Sudmann Einar | Prosthetic element |
GB0422666D0 (en) | 2004-10-12 | 2004-11-10 | Benoist Girard Sas | Prosthetic acetabular cups |
WO2006053291A2 (en) | 2004-11-09 | 2006-05-18 | Proxy Biomedical Limited | Tissue scaffold |
US20060254200A1 (en) | 2004-11-19 | 2006-11-16 | The Trustees Of Columbia University In The City Of New York | Systems and methods for construction of space-truss structures |
SG123615A1 (en) | 2004-12-10 | 2006-07-26 | Nanyang Polytechnic | Method for designing 3-dimensional porous tissue engineering scaffold |
US7879275B2 (en) | 2004-12-30 | 2011-02-01 | Depuy Products, Inc. | Orthopaedic bearing and method for making the same |
US7718109B2 (en) | 2005-02-14 | 2010-05-18 | Mayo Foundation For Medical Education And Research | Tissue support structure |
US8066778B2 (en) | 2005-04-21 | 2011-11-29 | Biomet Manufacturing Corp. | Porous metal cup with cobalt bearing surface |
US8292967B2 (en) | 2005-04-21 | 2012-10-23 | Biomet Manufacturing Corp. | Method and apparatus for use of porous implants |
US8029575B2 (en) | 2005-10-25 | 2011-10-04 | Globus Medical, Inc. | Porous and nonporous materials for tissue grafting and repair |
EP1779812A1 (en) | 2005-10-26 | 2007-05-02 | Etervind AB | An osseointegration implant |
US8308807B2 (en) | 2005-11-09 | 2012-11-13 | Zimmer, Gmbh | Implant with differential anchoring |
EP1949989B1 (en) | 2005-11-15 | 2012-01-11 | Panasonic Electric Works Co., Ltd. | Process for producing three-dimensionally shaped object |
US8728387B2 (en) | 2005-12-06 | 2014-05-20 | Howmedica Osteonics Corp. | Laser-produced porous surface |
US7578851B2 (en) | 2005-12-23 | 2009-08-25 | Howmedica Osteonics Corp. | Gradient porous implant |
EP1803513B1 (en) * | 2005-12-30 | 2017-03-29 | Howmedica Osteonics Corp. | Method of manufacturing implants using laser |
US20070156249A1 (en) | 2006-01-05 | 2007-07-05 | Howmedica Osteonics Corp. | High velocity spray technique for medical implant components |
US9327056B2 (en) | 2006-02-14 | 2016-05-03 | Washington State University | Bone replacement materials |
US8147861B2 (en) * | 2006-08-15 | 2012-04-03 | Howmedica Osteonics Corp. | Antimicrobial implant |
US20080161927A1 (en) | 2006-10-18 | 2008-07-03 | Warsaw Orthopedic, Inc. | Intervertebral Implant with Porous Portions |
EP1961433A1 (en) | 2007-02-20 | 2008-08-27 | National University of Ireland Galway | Porous substrates for implantation |
WO2008104599A1 (en) | 2007-02-28 | 2008-09-04 | Cinvention Ag | High surface cultivation system bag |
ITUD20070092A1 (en) | 2007-05-29 | 2008-11-30 | Lima Lto S P A | PROSTHETIC ELEMENT AND RELATIVE PROCEDURE FOR IMPLEMENTATION |
US8066770B2 (en) | 2007-05-31 | 2011-11-29 | Depuy Products, Inc. | Sintered coatings for implantable prostheses |
JP2010528765A (en) | 2007-06-07 | 2010-08-26 | スミス アンド ネフュー インコーポレーテッド | Reticulated particle porous coating for medical implant applications |
WO2009014718A1 (en) | 2007-07-24 | 2009-01-29 | Porex Corporation | Porous laser sintered articles |
US20110076316A1 (en) | 2007-10-08 | 2011-03-31 | Sureshan Sivananthan | Scalable matrix for the in vivo cultivation of bone and cartilage |
CA2704032C (en) | 2007-10-29 | 2016-10-18 | Zimmer, Inc. | Medical implants and methods for delivering biologically active agents |
US8979938B2 (en) | 2007-11-08 | 2015-03-17 | Linares Medical Devices, Llc | Artificial knee implant including liquid ballast supporting / rotating surfaces and incorporating flexible multi-material and natural lubricant retaining matrix applied to a joint surface |
AU2009205896A1 (en) | 2008-01-17 | 2009-07-23 | Synthes Gmbh | An expandable intervertebral implant and associated method of manufacturing the same |
WO2009116950A1 (en) | 2008-03-17 | 2009-09-24 | Nanyang Polytechnic | Mould for casting tissue engineering scaffolds and process for generating the same |
GB0809721D0 (en) | 2008-05-28 | 2008-07-02 | Univ Bath | Improvements in or relating to joints and/or implants |
CN100588379C (en) | 2008-06-26 | 2010-02-10 | 上海交通大学 | Preparation of artificial joint prosthesis with partially controllable porous structure |
US8696754B2 (en) | 2008-09-03 | 2014-04-15 | Biomet Manufacturing, Llc | Revision patella prosthesis |
KR20110090922A (en) | 2008-10-29 | 2011-08-10 | 스미스 앤드 네퓨, 인크. | Porous surface layers with increased surface roughness and implants incorporating the same |
ES2555487T3 (en) | 2008-12-18 | 2016-01-04 | 4-Web, Inc. | Lattice lattice structure implant |
US20110004447A1 (en) | 2009-07-01 | 2011-01-06 | Schlumberger Technology Corporation | Method to build 3D digital models of porous media using transmitted laser scanning confocal mircoscopy and multi-point statistics |
EP2253291B1 (en) | 2009-05-19 | 2016-03-16 | National University of Ireland, Galway | A bone implant with a surface anchoring structure |
WO2011022560A1 (en) | 2009-08-19 | 2011-02-24 | Smith & Nephew, Inc. | Porous implant structures |
US20110200478A1 (en) | 2010-02-14 | 2011-08-18 | Romain Louis Billiet | Inorganic structures with controlled open cell porosity and articles made therefrom |
IT1398443B1 (en) | 2010-02-26 | 2013-02-22 | Lima Lto S P A Ora Limacorporate Spa | INTEGRATED PROSTHETIC ELEMENT |
CA2802099A1 (en) | 2010-06-08 | 2011-12-15 | Smith & Nephew, Inc. | Implant components and methods |
US20110313532A1 (en) | 2010-06-18 | 2011-12-22 | Jessee Hunt | Bone implant interface system and method |
US9801974B2 (en) | 2010-08-13 | 2017-10-31 | Smith & Nephew, Inc. | Patellar implants |
US8727203B2 (en) | 2010-09-16 | 2014-05-20 | Howmedica Osteonics Corp. | Methods for manufacturing porous orthopaedic implants |
CN102087676B (en) | 2010-12-13 | 2012-07-04 | 上海大学 | Pore network model (PNM)-based bionic bone scaffold designing method |
WO2013006778A2 (en) | 2011-07-07 | 2013-01-10 | 4-Web, Inc. | Foot and ankle implant system and method |
US20130030529A1 (en) | 2011-07-29 | 2013-01-31 | Jessee Hunt | Implant interface system and method |
EP2773293B1 (en) | 2011-11-03 | 2017-08-30 | 4-web, Inc. | Implant for length preservation during bone repair |
CA2863865C (en) | 2012-02-08 | 2021-08-24 | 4-Web, Inc. | Prosthetic implant for ball and socket joints and method of use |
US9180010B2 (en) | 2012-04-06 | 2015-11-10 | Howmedica Osteonics Corp. | Surface modified unit cell lattice structures for optimized secure freeform fabrication |
US8843229B2 (en) | 2012-07-20 | 2014-09-23 | Biomet Manufacturing, Llc | Metallic structures having porous regions from imaged bone at pre-defined anatomic locations |
US9415137B2 (en) | 2012-08-22 | 2016-08-16 | Biomet Manufacturing, Llc. | Directional porous coating |
KR20150060828A (en) | 2012-09-25 | 2015-06-03 | 4웹, 인코포레이티드 | Programmable implants and methods of using programmable implants to repair bone structures |
US20140288650A1 (en) | 2013-03-15 | 2014-09-25 | 4Web, Inc. | Motion preservation implant and methods |
JP2016513551A (en) | 2013-03-15 | 2016-05-16 | マコ サージカル コーポレーション | Unicondylar tibial knee implant |
JP6573598B2 (en) | 2013-03-15 | 2019-09-11 | フォー−ウェブ・インコーポレイテッド | Traumatic fracture repair system and method |
US8983646B1 (en) | 2013-10-10 | 2015-03-17 | Barbara Hanna | Interactive digital drawing and physical realization |
US10842634B2 (en) | 2014-05-02 | 2020-11-24 | The Royal Institution For The Advancement Of Learning/Mcgill University | Structural porous biomaterial and implant formed of same |
US20150374882A1 (en) | 2014-06-20 | 2015-12-31 | Robert Anthony McDemus | Porous material |
US10881518B2 (en) | 2017-04-01 | 2021-01-05 | HD LifeSciences LLC | Anisotropic biocompatible lattice structure |
US11628517B2 (en) | 2017-06-15 | 2023-04-18 | Howmedica Osteonics Corp. | Porous structures produced by additive layer manufacturing |
US11071630B2 (en) | 2017-11-09 | 2021-07-27 | DePuy Synthes Products, Inc. | Orthopaedic prosthesis for an interphalangeal joint and associated method |
-
2003
- 2003-11-07 EP EP03257046A patent/EP1418013B1/en not_active Expired - Lifetime
- 2003-11-07 AU AU2003261497A patent/AU2003261497B2/en not_active Expired
- 2003-11-07 CA CA2448592A patent/CA2448592C/en not_active Expired - Lifetime
- 2003-11-07 US US10/704,270 patent/US7537664B2/en active Active
- 2003-11-07 AT AT03257046T patent/ATE287307T1/en not_active IP Right Cessation
- 2003-11-07 DE DE60300277T patent/DE60300277T2/en not_active Expired - Lifetime
-
2009
- 2009-04-22 US US12/386,679 patent/US8268099B2/en not_active Expired - Lifetime
-
2010
- 2010-07-26 US US12/843,376 patent/US8268100B2/en not_active Expired - Lifetime
-
2012
- 2012-09-06 US US13/605,354 patent/US8992703B2/en not_active Expired - Lifetime
-
2015
- 2015-03-27 US US14/671,545 patent/US10525688B2/en active Active
-
2019
- 2019-11-21 US US16/690,307 patent/US11155073B2/en not_active Expired - Lifetime
-
2021
- 2021-02-16 US US17/176,842 patent/US11186077B2/en not_active Expired - Lifetime
- 2021-08-13 US US17/401,977 patent/US11510783B2/en not_active Expired - Lifetime
Patent Citations (101)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US14403A (en) * | 1856-03-11 | Improved spirit blow-pipe | ||
US3605123A (en) * | 1969-04-29 | 1971-09-20 | Melpar Inc | Bone implant |
US3816855A (en) * | 1971-06-01 | 1974-06-18 | Nat Res Dev | Knee joint prosthesis |
US3806961A (en) * | 1972-02-16 | 1974-04-30 | Sulzer Ag | Phosthetic patella implant |
US4085466A (en) * | 1974-11-18 | 1978-04-25 | National Research Development Corporation | Prosthetic joint device |
US4202055A (en) * | 1976-05-12 | 1980-05-13 | Battelle-Institut E.V. | Anchorage for highly stressed endoprostheses |
US4164794A (en) * | 1977-04-14 | 1979-08-21 | Union Carbide Corporation | Prosthetic devices having coatings of selected porous bioengineering thermoplastics |
US4305340A (en) * | 1978-02-24 | 1981-12-15 | Yuwa Sangyo Kabushiki Kaisha | Method of forming a box-shaped structure from a foldable metal sheet |
US4218494A (en) * | 1978-07-04 | 1980-08-19 | Centro Richerche Fiat S.P.A. | Process for coating a metallic surface with a wear-resistant material |
US4385404A (en) * | 1980-02-21 | 1983-05-31 | J. & P. Coats, Limited | Device and method for use in the treatment of damaged articular surfaces of human joints |
US4344193A (en) * | 1980-11-28 | 1982-08-17 | Kenny Charles H | Meniscus prosthesis |
US4644942A (en) * | 1981-07-27 | 1987-02-24 | Battelle Development Corporation | Production of porous coating on a prosthesis |
US4502161A (en) * | 1981-09-21 | 1985-03-05 | Wall W H | Prosthetic meniscus for the repair of joints |
US4502161B1 (en) * | 1981-09-21 | 1989-07-25 | ||
US4673408A (en) * | 1983-08-24 | 1987-06-16 | Arthroplasty Research & Development (Pty) Ltd. | Knee prosthesis |
US4969907A (en) * | 1985-01-08 | 1990-11-13 | Sulzer Brothers Limited | Metal bone implant |
US4714473A (en) * | 1985-07-25 | 1987-12-22 | Harrington Arthritis Research Center | Knee prosthesis |
US5034186A (en) * | 1985-11-20 | 1991-07-23 | Permelec Electrode Ltd. | Process for providing titanium composite having a porous surface |
US4636219A (en) * | 1985-12-05 | 1987-01-13 | Techmedica, Inc. | Prosthesis device fabrication |
US4714474A (en) * | 1986-05-12 | 1987-12-22 | Dow Corning Wright Corporation | Tibial knee joint prosthesis with removable articulating surface insert |
US4961154A (en) * | 1986-06-03 | 1990-10-02 | Scitex Corporation Ltd. | Three dimensional modelling apparatus |
US4719908A (en) * | 1986-08-15 | 1988-01-19 | Osteonics Corp. | Method and apparatus for implanting a prosthetic device |
US4944817A (en) * | 1986-10-17 | 1990-07-31 | Board Of Regents, The University Of Texas System | Multiple material systems for selective beam sintering |
US5616294A (en) * | 1986-10-17 | 1997-04-01 | Board Of Regents, The University Of Texas System | Method for producing parts by infiltration of porous intermediate parts |
US5017753A (en) * | 1986-10-17 | 1991-05-21 | Board Of Regents, The University Of Texas System | Method and apparatus for producing parts by selective sintering |
US4863538A (en) * | 1986-10-17 | 1989-09-05 | Board Of Regents, The University Of Texas System | Method and apparatus for producing parts by selective sintering |
US5155324A (en) * | 1986-10-17 | 1992-10-13 | Deckard Carl R | Method for selective laser sintering with layerwise cross-scanning |
US5076869A (en) * | 1986-10-17 | 1991-12-31 | Board Of Regents, The University Of Texas System | Multiple material systems for selective beam sintering |
US5386500A (en) * | 1987-06-02 | 1995-01-31 | Cubital Ltd. | Three dimensional modeling apparatus |
US5287435A (en) * | 1987-06-02 | 1994-02-15 | Cubital Ltd. | Three dimensional modeling |
US5735903A (en) * | 1987-07-20 | 1998-04-07 | Li; Shu-Tung | Meniscal augmentation device |
US5158574A (en) * | 1987-07-20 | 1992-10-27 | Regen Corporation | Prosthetic meniscus |
US5031120A (en) * | 1987-12-23 | 1991-07-09 | Itzchak Pomerantz | Three dimensional modelling apparatus |
US5080674A (en) * | 1988-09-08 | 1992-01-14 | Zimmer, Inc. | Attachment mechanism for securing an additional portion to an implant |
US4990163A (en) * | 1989-02-06 | 1991-02-05 | Trustees Of The University Of Pennsylvania | Method of depositing calcium phosphate cermamics for bone tissue calcification enhancement |
US5053090A (en) * | 1989-09-05 | 1991-10-01 | Board Of Regents, The University Of Texas System | Selective laser sintering with assisted powder handling |
US5192328A (en) * | 1989-09-29 | 1993-03-09 | Winters Thomas F | Knee joint replacement apparatus |
US5024670A (en) * | 1989-10-02 | 1991-06-18 | Depuy, Division Of Boehringer Mannheim Corporation | Polymeric bearing component |
US5004476A (en) * | 1989-10-31 | 1991-04-02 | Tulane University | Porous coated total hip replacement system |
US5067964A (en) * | 1989-12-13 | 1991-11-26 | Stryker Corporation | Articular surface repair |
US5171282A (en) * | 1990-01-12 | 1992-12-15 | Societe Civile D'innovations Technologique | Femoral member for knee prosthesis |
US5108432A (en) * | 1990-06-24 | 1992-04-28 | Pfizer Hospital Products Group, Inc. | Porous fixation surface |
US5702448A (en) * | 1990-09-17 | 1997-12-30 | Buechel; Frederick F. | Prosthesis with biologically inert wear resistant surface |
US5147402A (en) * | 1990-12-05 | 1992-09-15 | Sulzer Brothers Limited | Implant for ingrowth of osseous tissue |
US5323954A (en) * | 1990-12-21 | 1994-06-28 | Zimmer, Inc. | Method of bonding titanium to a cobalt-based alloy substrate in an orthophedic implant device |
US5176710A (en) * | 1991-01-23 | 1993-01-05 | Orthopaedic Research Institute | Prosthesis with low stiffness factor |
US5219362A (en) * | 1991-02-07 | 1993-06-15 | Finsbury (Instruments) Limited | Knee prosthesis |
US5314478A (en) * | 1991-03-29 | 1994-05-24 | Kyocera Corporation | Artificial bone connection prosthesis |
US5571185A (en) * | 1991-10-12 | 1996-11-05 | Eska Implants Gmbh | Process for the production of a bone implant and a bone implant produced thereby |
US5282870A (en) * | 1992-01-14 | 1994-02-01 | Sulzer Medizinaltechnik Ag | Artificial knee joint |
US5609646A (en) * | 1992-01-23 | 1997-03-11 | Howmedica International | Acetabular cup for a total hip prosthesis |
US5282861A (en) * | 1992-03-11 | 1994-02-01 | Ultramet | Open cell tantalum structures for cancellous bone implants and cell and tissue receptors |
US5496372A (en) * | 1992-04-17 | 1996-03-05 | Kyocera Corporation | Hard tissue prosthesis including porous thin metal sheets |
US5824102A (en) * | 1992-06-19 | 1998-10-20 | Buscayret; Christian | Total knee prosthesis |
US5648450A (en) * | 1992-11-23 | 1997-07-15 | Dtm Corporation | Sinterable semi-crystalline powder and near-fully dense article formed therein |
US5728162A (en) * | 1993-01-28 | 1998-03-17 | Board Of Regents Of University Of Colorado | Asymmetric condylar and trochlear femoral knee component |
US5368602A (en) * | 1993-02-11 | 1994-11-29 | De La Torre; Roger A. | Surgical mesh with semi-rigid border members |
US5358529A (en) * | 1993-03-05 | 1994-10-25 | Smith & Nephew Richards Inc. | Plastic knee femoral implants |
US5443510A (en) * | 1993-04-06 | 1995-08-22 | Zimmer, Inc. | Porous coated implant and method of making same |
US5443518A (en) * | 1993-07-20 | 1995-08-22 | Zimmer, Inc. | Knee position indicator |
US5398193A (en) * | 1993-08-20 | 1995-03-14 | Deangelis; Alfredo O. | Method of three-dimensional rapid prototyping through controlled layerwise deposition/extraction and apparatus therefor |
US5398193B1 (en) * | 1993-08-20 | 1997-09-16 | Alfredo O Deangelis | Method of three-dimensional rapid prototyping through controlled layerwise deposition/extraction and apparatus therefor |
US5549700A (en) * | 1993-09-07 | 1996-08-27 | Ortho Development Corporation | Segmented prosthetic articulation |
US5490962A (en) * | 1993-10-18 | 1996-02-13 | Massachusetts Institute Of Technology | Preparation of medical devices by solid free-form fabrication methods |
US5773789A (en) * | 1994-04-18 | 1998-06-30 | Bristol-Myers Squibb Company | Method of making an orthopaedic implant having a porous metal pad |
US5504300A (en) * | 1994-04-18 | 1996-04-02 | Zimmer, Inc. | Orthopaedic implant and method of making same |
US6049054A (en) * | 1994-04-18 | 2000-04-11 | Bristol-Myers Squibb Company | Method of making an orthopaedic implant having a porous metal pad |
US5973222A (en) * | 1994-04-18 | 1999-10-26 | Bristol-Myers Squibb Co. | Orthopedic implant having a porous metal pad |
US5795353A (en) * | 1994-05-06 | 1998-08-18 | Advanced Bio Surfaces, Inc. | Joint resurfacing system |
US6248131B1 (en) * | 1994-05-06 | 2001-06-19 | Advanced Bio Surfaces, Inc. | Articulating joint repair |
US5879387A (en) * | 1994-08-25 | 1999-03-09 | Howmedica International Inc. | Prosthetic bearing element and method of manufacture |
US5989472A (en) * | 1994-10-05 | 1999-11-23 | Howmedica International, Inc. | Method for making a reinforced orthopedic implant |
US5571196A (en) * | 1994-10-24 | 1996-11-05 | Stein; Daniel | Patello-femoral joint replacement device and method |
US5824098A (en) * | 1994-10-24 | 1998-10-20 | Stein; Daniel | Patello-femoral joint replacement device and method |
US5514183A (en) * | 1994-12-20 | 1996-05-07 | Epstein; Norman | Reduced friction prosthetic knee joint utilizing replaceable roller bearings |
US5879398A (en) * | 1995-02-14 | 1999-03-09 | Zimmer, Inc. | Acetabular cup |
US5782908A (en) * | 1995-08-22 | 1998-07-21 | Medtronic, Inc. | Biocompatible medical article and method |
US5776201A (en) * | 1995-10-02 | 1998-07-07 | Johnson & Johnson Professional, Inc. | Modular femoral trial system |
US5640667A (en) * | 1995-11-27 | 1997-06-17 | Board Of Regents, The University Of Texas System | Laser-directed fabrication of full-density metal articles using hot isostatic processing |
US5681354A (en) * | 1996-02-20 | 1997-10-28 | Board Of Regents, University Of Colorado | Asymmetrical femoral component for knee prosthesis |
US6087553A (en) * | 1996-02-26 | 2000-07-11 | Implex Corporation | Implantable metallic open-celled lattice/polyethylene composite material and devices |
US6046426A (en) * | 1996-07-08 | 2000-04-04 | Sandia Corporation | Method and system for producing complex-shape objects |
US6215093B1 (en) * | 1996-12-02 | 2001-04-10 | Fraunhofer-Gesellschaft Zur Foerderung Der Angewandten Forschung E.V. | Selective laser sintering at melting temperature |
US6280478B1 (en) * | 1997-03-04 | 2001-08-28 | Implico B.V. | Artefact suitable for use as a bone implant |
US5928285A (en) * | 1997-05-30 | 1999-07-27 | Bristol-Myers Squibb Co. | Orthopaedic implant having an articulating surface with a conforming and translational surface |
US6355086B2 (en) * | 1997-08-12 | 2002-03-12 | Rolls-Royce Corporation | Method and apparatus for making components by direct laser processing |
US20010014403A1 (en) * | 1997-08-12 | 2001-08-16 | Lawrence Evans Brown | Method and apparatus for making components by direct laser processing |
US6190407B1 (en) * | 1997-11-20 | 2001-02-20 | St. Jude Medical, Inc. | Medical article with adhered antimicrobial metal |
US6139585A (en) * | 1998-03-11 | 2000-10-31 | Depuy Orthopaedics, Inc. | Bioactive ceramic coating and method |
US20020016635A1 (en) * | 1998-05-14 | 2002-02-07 | Hayes Medical, Inc. | Implant with composite coating |
US6261322B1 (en) * | 1998-05-14 | 2001-07-17 | Hayes Medical, Inc. | Implant with composite coating |
US6132468A (en) * | 1998-09-10 | 2000-10-17 | Mansmann; Kevin A. | Arthroscopic replacement of cartilage using flexible inflatable envelopes |
US6283997B1 (en) * | 1998-11-13 | 2001-09-04 | The Trustees Of Princeton University | Controlled architecture ceramic composites by stereolithography |
US6096043A (en) * | 1998-12-18 | 2000-08-01 | Depuy Orthopaedics, Inc. | Epicondylar axis alignment-femoral positioning drill guide |
US6395327B1 (en) * | 1999-03-12 | 2002-05-28 | Zimmer, Inc. | Enhanced fatigue strength orthopaedic implant with porous coating and method of making same |
US20020151983A1 (en) * | 1999-03-12 | 2002-10-17 | Shetty H. Ravindranath | Enhanced fatigue strength orthopaedic implant with porous coating and method of making same |
US6206927B1 (en) * | 1999-04-02 | 2001-03-27 | Barry M. Fell | Surgically implantable knee prothesis |
US6251143B1 (en) * | 1999-06-04 | 2001-06-26 | Depuy Orthopaedics, Inc. | Cartilage repair unit |
US6299645B1 (en) * | 1999-07-23 | 2001-10-09 | William S. Ogden | Dove tail total knee replacement unicompartmental |
US6206924B1 (en) * | 1999-10-20 | 2001-03-27 | Interpore Cross Internat | Three-dimensional geometric bio-compatible porous engineered structure for use as a bone mass replacement or fusion augmentation device |
US6371958B1 (en) * | 2000-03-02 | 2002-04-16 | Ethicon, Inc. | Scaffold fixation device for use in articular cartilage repair |
Cited By (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20110143094A1 (en) * | 2009-12-11 | 2011-06-16 | Ngimat Co. | Process for Forming High Surface Area Embedded Coating with High Abrasion Resistance |
US8834964B2 (en) * | 2009-12-11 | 2014-09-16 | Ngimat, Co. | Process for forming high surface area embedded coating with high abrasion resistance |
EP2817037B1 (en) * | 2012-02-20 | 2022-08-03 | Smith & Nephew, Inc. | Methods of making porous structures |
US20170021453A1 (en) * | 2013-12-23 | 2017-01-26 | General Electric Technology Gmbh | Gamma prime precipitation strengthened nickel-base superalloy for use in powder based additive manufacturing process |
US20150321289A1 (en) * | 2014-05-12 | 2015-11-12 | Siemens Energy, Inc. | Laser deposition of metal foam |
US11897033B2 (en) | 2018-04-19 | 2024-02-13 | Compagnie Generale Des Etablissements Michelin | Process for the additive manufacturing of a three-dimensional metal part |
US11167375B2 (en) | 2018-08-10 | 2021-11-09 | The Research Foundation For The State University Of New York | Additive manufacturing processes and additively manufactured products |
US11426818B2 (en) | 2018-08-10 | 2022-08-30 | The Research Foundation for the State University | Additive manufacturing processes and additively manufactured products |
WO2021097248A1 (en) * | 2019-11-14 | 2021-05-20 | University Of Washington | Closed-loop feedback for additive manufacturing simulation |
Also Published As
Publication number | Publication date |
---|---|
ATE287307T1 (en) | 2005-02-15 |
AU2003261497B2 (en) | 2009-02-26 |
EP1418013B1 (en) | 2005-01-19 |
US8268100B2 (en) | 2012-09-18 |
US20100291286A1 (en) | 2010-11-18 |
US11186077B2 (en) | 2021-11-30 |
US10525688B2 (en) | 2020-01-07 |
US20200086625A1 (en) | 2020-03-19 |
US11510783B2 (en) | 2022-11-29 |
US20210162731A1 (en) | 2021-06-03 |
US20040191106A1 (en) | 2004-09-30 |
EP1418013A1 (en) | 2004-05-12 |
US20150258735A1 (en) | 2015-09-17 |
US8268099B2 (en) | 2012-09-18 |
US7537664B2 (en) | 2009-05-26 |
CA2448592C (en) | 2011-01-11 |
US20210379884A1 (en) | 2021-12-09 |
DE60300277D1 (en) | 2005-02-24 |
US11155073B2 (en) | 2021-10-26 |
US8992703B2 (en) | 2015-03-31 |
DE60300277T2 (en) | 2006-01-12 |
AU2003261497A1 (en) | 2004-05-27 |
CA2448592A1 (en) | 2004-05-08 |
US20130056912A1 (en) | 2013-03-07 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US8268099B2 (en) | Laser-produced porous surface | |
US10716673B2 (en) | Laser-produced porous surface | |
Wang et al. | Study on the designing rules and processability of porous structure based on selective laser melting (SLM) | |
EP1683593A2 (en) | Laser produced porous structure | |
AU2019244702A1 (en) | Three-dimensional porous structures for bone ingrowth and methods for producing | |
US11918474B2 (en) | Laser-produced porous surface | |
AU2012216789B2 (en) | Laser-produced porous surface | |
Abd Aziz | Direct Metal Laser Sintering of Titanium Implant with Tailored Structure and Mechanical Properties | |
Miura et al. | Direct laser forming for more complex shaped titanium alloy compacts |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: HOWMEDICA OSTEONICS CORP., NEW JERSEY Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:O'NEILL, WILLIAM;SUTCLIFFE, CHRISTOPHER J.;JONES, ERIC;REEL/FRAME:028563/0182 Effective date: 20040617 |
|
STCF | Information on status: patent grant |
Free format text: PATENTED CASE |
|
AS | Assignment |
Owner name: LIVERPOOL, UNIVERSITY OF THE, UNITED KINGDOM Free format text: CONFIRMATORY ASSIGNMENT OF 50% INTEREST FOR HOWMEDICA OSTEONICS CORP. AND 50% INTEREST FOR THE UNIVERSITY OF LIVERPOOL;ASSIGNOR:HOWMEDICA OSTEONICS CORP.;REEL/FRAME:031662/0726 Effective date: 20060103 Owner name: THE UNIVERSITY OF LIVERPOOL, UNITED KINGDOM Free format text: CONFIRMATORY ASSIGNMENT OF 50% INTEREST FOR HOWMEDICA OSTEONICS CORP. AND 50% INTEREST FOR THE UNIVERSITY OF LIVERPOOL;ASSIGNOR:HOWMEDICA OSTEONICS CORP.;REEL/FRAME:031662/0726 Effective date: 20060103 |
|
FPAY | Fee payment |
Year of fee payment: 4 |
|
MAFP | Maintenance fee payment |
Free format text: PAYMENT OF MAINTENANCE FEE, 8TH YEAR, LARGE ENTITY (ORIGINAL EVENT CODE: M1552); ENTITY STATUS OF PATENT OWNER: LARGE ENTITY Year of fee payment: 8 |